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"BREATHING ASSISTANCE APPARATUS"
BACKGROUND OF THE INVENTION
Field of the Invention
This invention relates to a breathing gases supply and gases humidification
apparatus and a method of controlling such apparatus. Uses for the breathing assistance
apparatus of the present invention are the supply of gases for any medical condition or
treatment that results in the drying of the upper airways, and/or salivary glands, such as
head or neck radiotherapy or long term oxygen therapy. Further uses are for medical
conditions that result in impaired mucociliary clearance systems such as Chronic
Obstructive Pulmonary Disease (COPD) or bronchiectasis or in the supply of Continuous
Positive Airway Pressure (CPAP) to treat Obstructive Sleep Apnoea (OSA) or other
respiratory conditions.
Summary of the Prior Art
A number of methods are known in the art for assisting a patient's breathing.
Continuous Positive Airway Pressure (CPAP) involves the administration of air under
pressure to a patient, usually by a nasal mask. Tt is used in the treatment of snoring and
Obstructive Sleep Apnoea (OSA), a condition characterised by repetitive collapse of the
upper airway during inspiration. Positive pressure splints the upper airway open,
preventing its collapse. Treatment of OSA with nasal CPAP has proven to be both
effective and safe, but CPAP is difficult to use and the majority of patients experience
significant side effects, particularly in the early stages of treatment.
CPAP is also commonly used for patients with a variety of respiratory illnesses,
including COPD.
Upper airway symptoms adversely affect treatment with CPAP. Mucosal drying is
uncomfortable and may awaken patients during the night. Rebound nasal congestion
commonly occurs during the following day, simulating a viral infection. If untreated,
upper airway symptoms adversely affect rates of CPAP use.
Increases in nasal resistance may affect the level of CPAP treatment delivered to
the pharynx, and reduce the effectiveness of treatment. An individual pressure is
determined for each patient using CPAP and this pressure is set at the patient interface.
Changes in nasal resistance affect pressure delivered to the pharynx and if the changes are
of sufficient magnitude there may be recurrence of snoring or airway collapse or reduce the

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level of pressure applied to the lungs. Such symptoms can also occur in a hospital
environment where a patient is on a respirator. Typically in such situations the patient is
intubated. Therefore the throat tissue may become irritated and inflamed causing both
distress to the patient and possible further respiratory problems.
A number of methods may be employed to treat such upper airway symptoms,
including pharmacological agents to reduce nasal disease, or heating the bedroom. One
most commonly employed method is humidification of the inspired air using an in line
humidifier. Two types of humidifier are currently used. Cold pass-over humidifiers rely on
humidifying the air through exposure to a large surface area of water. While they are
cheap, the humidity output is low at high flows, typically 2 to 4 mg\L absolute humidity at
flows above 25L/min. The output is insufficient to prevent mucosal drying. Heated water
bath humidifiers are more efficient, and produce high levels of humidity even at high flow
rates. They are effective at preventing upper airway mucosal drying, prevent increases in
nasal resistance, and are the most reliable means of treating upper airway symptoms.
Oxygen is the most common drug prescribed to hospitalized patients. The delivery
of oxygen via nasal cannula or facemask is of benefit to a patient complaining of
breathlessness. By increasing the fraction of inspired oxygen, oxygen therapy reduces the
effort to breathe and can correct resulting hypoxia (a low level of oxygen in the tissues).
The duration of the therapy depends on the underlying illness. For example,
postoperative patients may only receive oxygen while recovering from surgery while
patients with COPD require oxygen 16 to 18 hours per day.
Currently greater than 16 million adults are afflicted with COPD, an umbrella term
which describes a group of lung diseases characterized by irreversible airflow limitation
that is associated mainly with emphysema and chronic bronchitis, most commonly caused
by smoking over several decades. When airway limitation is moderately advanced, it
manifests as perpetual breathlessness, without physical exertion. Situations such as a
tracheobronchial infection, heart failure and also environmental exposure can incite an
exacerbation of COPD that requires hospitalization until the acute breathlessness is under
control. During an acute exacerbation of COPD, the patient experiences an increase in
difficulty of breathing (dyspnea), hypoxia, and increase in sputum volume and purulence
and increased coughing.
Oxygen therapy provides enormous benefit to patients with an acute exacerbation
of COPD who are hypoxic, by decreasing the risk of vital organ failure and reducing

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dyspnea. The major complication associated with oxygen therapy is hypercarpnia (an
elevation in blood carbon dioxide levels) and subsequent respiratory failure. Therefore, the
dose of oxygen administered can be critical and must be precisely known.
To accurately control the oxygen dose given to a patient, the oxygen-enriched gas
must exceed the patient's peak inspiratory flow to prevent the entrainment of room air and
dilution of the oxygen. To achieve this, flows of greater than 20 L/min are common. Such
flows of dry gases cause dehydration and inflammation of the nasal passages and airways
if delivered by nasal cannula. To avoid this occurrence, a heated humidifier is used.
The majority of systems that are used for oxygen therapy or merely deliver)' of
gases to a patient consists of a gases supply, a humidifier and conduit. Interfaces include
face masks, oral mouthpieces, tracheostomy inlets and nasal cannula, the latter having the
advantage of being more comfortable and acceptable than a facemask.
It is usual for the gases supply to provide a constant, prescribed level of gases flow
to the humidifier. The humidifier and conduit can then heat and humidify the gases to a set
temperature and humidity before delivery to the patient. It is important to note that the
warm-up time required from start-up for the gases to reach optimal temperature and
humidity increases with higher flow rates. The operating instructions of such a system
commonly instruct the user not to connect the system to the patient until the humidifier has
completed the warm-up period. Thereafter, patients receive up to 40L/min of near body
temperature saturated gases. Patients often feel overwhelmed by sudden delivery of high
flow at this time.
A group of patients who would benefit from humidification therapy are patients
who have mucociliary clearance deficiencies. These patients often have purulent mucus
and are susceptible to infections from pathogens. Heated humidified air with an abundance
of water particles is an ideal medium to harbour disease carrying pathogens.
Consequently, considerable design expertise has been required to provide the market with
active pass-over humidifiers that deliver water molecules, in gas phase only, so that it is
not possible for disease pathogens to be carried in air to the patient. Water that condenses
on the inner surfaces of the breathing circuit or conduit at the end of a treatment session
may harbour pathogens that would be delivered to the patient next time they use the
device. This is particularly the case with therapies for COPD patients that are receiving
body temperature fully saturated air.

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The hygiene of a breathing circuit (the tubing supplying humidified gases to a
patient) is particularly important when the humidification therapy is used for the treatment
of respiratory diseases. Any moisture remaining in the breathing circuit at the end of a
treatment may harbour pathogens exhaled or expelled (as mucus may be expelled into the
circuit or patient interface) by the patient. This moisture provides a means to transport the
pathogens in the tubing providing a source of further infection for the patient when the
tubing is next used. Often with such treatment the tubing is not cleaned daily and therefore
must be thoroughly dried at the end of treatment. This cleaning is time consuming and will
not always be earned out to precise instructions.
DISCLOSURE OF THE INVENTION
It is an object of the present invention to provide a breathing assistance apparatus
which goes some way to overcoming the abovementioned disadvantages or which at least
provides the public or industry with a useful choice.
Accordingly in a first aspect the present invention consists in a breathing assistance
apparatus adapted to deliver humidified gases at a desired level of humidity, flow and
temperature for treatment of a patient comprising:
a) gases supply means providing a flow of gases,
b) a humidifier having a chamber adapted to receive a volume of water and a
chamber heater to heat said water in said chamber, said chamber including an inlet and an
outlet,
c) transportation pathway means to convey said humidified gases from said
humidifier to said patient,
d) a controller having stored instructions to complete the following steps at the
end of said treatment of said patient:
i) switch off power to said chamber heater,
ii) set said flow of gases from said gases supply means to a
predetermined flow for a predetermined time,
iii) after said predetermined time switch off said gases supply means.
Preferably said transportation pathway means has a pathway heater, and said
apparatus further comprises:
a) an outlet temperature sensor measuring the temperature of said gases at said
outlet to said chamber,

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b) a distal temperature sensor measuring the temperature of said gases at the
distal end of the transportation pathway means,
c) an ambient temperature sensor measuring ambient air temperature, and said
controller includes stored instructions to:
i) control said pathway heater over said predetermined time such that
the temperature of said gases at the distal end of said transportation pathway means, as
sensed by said second sensor does not exceed a safe temperature level, and
ii) monitor said outlet gases temperature sensor and said ambient air
temperature sensor, compare said outlet gases temperature and said ambient air
temperature and when these are substantially equal end said predetermined time and switch
of said gases supply means and said pathway heater.
Preferably said transportation pathway means has a pathway heater, and said
apparatus further comprises:
a) a distal temperature sensor measuring the temperature of said gases at the
distal end of the transportation pathway means,
b) an ambient temperature sensor measuring ambient air temperature,
c) a chamber heater temperature sensor measuring said chamber heater
temperature, and said controller includes stored instructions to:
i) control said pathway heater over said predetermined time such that
the temperature of said gases at the distal end of said transportation pathway means, as
sensed by said second sensor does not exceed a safe temperature level, and
ii) monitor said chamber heater temperature sensor and ambient air
temperature sensor, compare said chamber heater temperature and said ambient air
temperature and when these are substantially equal end said predetermined time and switch
off said gases supply means and said pathway heater.
Preferably said transportation pathway means is an extruded plastic tube, and said
pathway heater is at least two conductive wires embedded within, throughout or about the
wall of said tube.
Preferably said controller includes stored instructions to determine said end of said
treatment when said patient activates an "off button connected to said controller.
Alternatively said apparatus further comprises a patient interface sensor, and said
controller includes stored instructions to determine said end of said treatment when said

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patient interface sensor detects that said patient has removed said patient interface for a
predetermined period of time.
Alternatively said controller includes stored instructions to determine said end of
treatment when a substantial increase of flow of gases is detected exiting said gas supply
means for a predetermined period of time.
Alternatively said apparatus further comprises a patient interface sensor, and said
controller includes stored instructions to determine said end of treatment when said patient
interface sensor senses that said patient's breathing through said patient interface has
ceased for a predetermined period of time.
In a second aspect the present invention consists in a method of controlling a
breathing assistance apparatus where said apparatus is adapted to deliver humidified gases
at a desired level of humidity, flow and temperature for treatment of a patient, said
apparatus comprising a gases supply means providing a flow of gases, a humidifier having
a chamber adapted to receive a volume of water and a chamber heater to heat said water in
said chamber, transportation pathway means to convey said humidified gases from said
humidifier to said patient, and a controller that stores a program which causes the
controller at the end of said treatment of said patient to:
a) switch off power to said chamber heater,
b) set said flow of gases from said gases supply means to a predetermined flow
for a predetermined time,
c) after said predetermined time switch off said gases supply means.
Preferably said transportation pathway means has a pathway heater, and said
apparatus further comprises an outlet temperature sensor measuring the temperature of said
gases at said outlet to said chamber, a distal temperature sensor measuring the temperature
of said gases at the distal end of the transportation pathway means, an ambient temperature
sensor measuring ambient air temperature, and said program further causes said
controller to:
a) control said pathway heater over said predetermined time such that the
temperature of said gases at the distal end of said transportation pathway means, as sensed
by said second sensor does not exceed a safe temperature level, and
b) monitor said outlet gases temperature sensor and said ambient air
temperature sensor, compare said outlet gases temperature and said ambient air

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temperature and when these are substantially equal end said predetermined time and switch
of said gases supply means and said pathway heater.
Preferably said transportation pathway means has a pathway heater, and said
apparatus further comprises a distal temperature sensor measuring the temperature of said
gases at the distal end of the transportation pathway means, an ambient temperature sensor
measuring ambient air temperature, a chamber heater temperature sensor measuring said
chamber heater temperature, and said program further causes said controller to:
a) control said pathway heater over said predetermined time such that the
temperature of said gases at the distal end of said transportation pathway means, as sensed
by said second sensor does not exceed a safe temperature level, and
b) monitor said chamber heater temperature sensor and ambient air
temperature sensor, compare said chamber heater temperature and said ambient air
temperature and when these are substantially equal end said predetermined time and switch
off said gases supply means and said pathway heater.
Preferably said program further causes said controller to determine said end of
said treatment when said patient activates an "off' button connected to said controller.
Alternatively said apparatus further comprises a patient interface sensor and said
program further causes said controller to determine said end of said treatment when said
patient interface sensor detects that said patient has removed said patient interface for a
predetermined period of time.
Alternatively said program further causes said controller to determine said end of
treatment when a substantial increase of flow of gases is detected exiting said gas supply
means for a predetermined period of time.
Alternatively said apparatus further comprises a patient interface sensor and said
program further causes said controller to determine said end of treatment when said
patient interface sensor senses that said patient's breathing through said patient interface
has ceased for a predetermined period of time.
To those skilled in the art to which the invention relates, many changes in
construction and widely differing embodiments and applications of the invention will
suggest themselves without departing from the scope of the invention as defined in the
appended claims. The disclosures and the descriptions herein are purely illustrative and
are not intended to be in any sense limiting.

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In this specification where reference has been made to patent specifications, other
external documents, or other sources of information, this is generally for the purpose of
providing a context for discussing the features of the invention. Unless specifically stated
otherwise, reference to such external documents is not to be construed as an admission that
such documents, or such sources of information, in any jurisdiction, are prior art, or form
part of the common general knowledge in the art.
BRIEF DESCRIPTION OF THE DRAWINGS
Preferred forms of the present invention will now be described with reference to the
accompanying drawings.
Figure 1 is an illustration of the breathing assistance apparatus that the control
method of the present invention may be used with.
Figure 2 is a perspective view of a combined gases supply and humidifier of the
breathing assistance apparatus of the present invention.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
A breathing assistance apparatus and method of controlling a breathing assistance
apparatus is detailed below. Particularly, the breathing assistance apparatus is controlled
such that it has a drying cycle to enable drying of the tubing that supplies gases to a user
and prevent the harbouring of pathogens within the tube. The drying cycle is preferably
operated automatically by internal controllers in the apparatus. However, it may be
manually activated by pressing a button on the apparatus. The drying cycle is preferably
activated at the end of a patient's treatment session.
The breathing assistance apparatus of the present invention is intended to typically
deliver body temperature saturated gases (37°C and 44mg/L) over a range of flows that
could provide up to a patient's inspiratory flow requirements (that is, peak inspiratory
flow) plus any bias flow requirement.
The breathing assistance apparatus operates as a flow controlled device, so it
adjusts the flow of gases to the level set by the patient or user, such as a care giver.
Therefore, this apparatus can be used to deliver humidified gas for patients with bypassed
airways, such as tracheotomies or nasal cannula or masks.
Whether used in a hospital environment or in a home care environment, the
breathing assistance apparatus of the present invention will generally have associated with
it a gases supply means, such as ambient air, gases, such as oxygen from cylinders or other

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compressed gas supply, humidification means and a transport conduit from the
humidification means to the patient, which is preferably heated to reduce condensation.
A heating element is preferably provided within the transport conduit to help
prevent condensation of the humidified gases within the conduit. Such condensation is due
to the temperature of the walls of the conduit being lower than to the dew point of the
gases inside the conduit, which is usually lower than the temperature of the humidified
gases within the conduit. The heating element effectively replaces the energy lost from the
gases through conduction and convection during transit through the conduit and the patient
interface. Thus the conduit heating element ensures the gases delivered are at an optimal
temperature and humidity for patient treatment and to minimise condensation within the
transport conduit and the patient interface.
The present invention provides a breathing assistance apparatus where the flow of
gases passes in sequence through a gases supply means or flow driver (such as, a blower,
fan or compressor), humidification chamber, heated delivery circuit and patient interface,
such as that shown in Figure 1.
With reference to Figure 1 the humidification apparatus of the present invention is
shown in which a patient 1 is receiving humidified and pressurised gases through a nasal
cannula 20 connected to a humidified gases transportation pathway or inspiratory conduit 3
that in turn is connected to a humidifier 8 (including humidification chamber 5) that is
supplied with gases from a blower 15 or other appropriate gases supply means. The
inspiratory conduit 3 is connected to the outlet 4 of a humidification chamber 5 which
contains a volume of water 6. Inspiratory conduit 3 contains heating means or heater wires
11 that heat the walls of the conduit to reduce condensation of humidified gases within the
conduit and the patient interface (e.g. nasal cannula 20). The humidification chamber 5 is
preferably formed from a plastics material and may have a highly heat conductive base (for
example an aluminium base) which is in direct contact with a heater plate 7 of humidifier
8. The humidifier 8 is provided with control means or electronic controller 9 which may
comprise a microprocessor based controller executing computer software commands stored
in associated memory.
Gases flowing through the inspiratory conduit 3 are passed to the patient by way of
a patient interface 20. The patient interface used with the apparatus of the present
invention may be a full-face mask, nasal mask, nasal cannula, oral mouthpiece or
tracheostomy connection.

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Controller 9 receives input from sources such as user input means or dial 10
through which a user of the device may, for example, set a predetermined required value
(preset value) of humidity or temperature of the gases supplied to patient 1. In response to
the user set humidity or temperature value input via dial (or buttons) 10 and other possible
inputs such as internal sensors that sense gases flow or temperature, or by parameters
calculated in the controller, controller 9 determines when (or to what level) to energise
heater plate 7 to heat the water 6 within huvnidification chamber 5. As the volume of water
6 within humidification chamber 5 is heated, water vapour begins to fill the volume of the
chamber above the water's surface and is passed out of the humidification chamber 5 outlet
4 with the flow of gases (for example air) provided from a gases supply means or blower
15 which enters the chamber 5 through inlet 16. It should be noted that it is possible to
obtain the relationship between the humidity of the gases in humidification chamber 5 and
the temperature of the heater plate 7. Accordingly, it is possible to utilise the heater plate
temperature in an algorithm or a look-up table to determine the humidity of the gases.
It is also possible to measure the chamber outlet gases temperature from the
humidification chamber 5 using a temperature sensor 12 and use this to determine the
humidity of the gases in the chamber 5 and conduit 3.
The blower 15 may be provided with a variable speed pump or fan 2 which draws
air or other gases through the blower inlet 17. Tire speed of variable speed pump or fan 2
may be controlled by a further control means or electronic controller 18 (or alternatively
the function of this controller 18 could be carried out by the other controller 9) in response
to inputs from controller 9 and a user set predetermined required value (preset value) of
pressure or fan speed via dial 19.
In the preferred embodiment shown in Figure 2 the breathing assistance apparatus
of the present invention the gases supply or blower is combined in one housing with the
humidifier and humidification chamber. The humidification chamber 35 extends out from
the housing 30 and is capable in use of being removed and replaced by the patient or other
user. Also, the inlet port (not shown) to the humidification chamber 35 is internal within
the housing 30. The inlet 31 to the housing 30 where gases are drawn from the ambient air
outside the housing 30 is located at the end of the housing 30, but in actuality may be
located at any appropriate point in the housing 30. The gases exit from the humidification
chamber 35 at the outlet 33 and water within the chamber 35 is heated by a heater plate 36,
similar to that described above. It must be appreciated that the embodiment described

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above in relation to the housing and Figure 2 merely illustrates one form of the housing of
the combined gases supply and humidifier of the present invention.
In one preferred form of the apparatus of the present invention, a nasal cannula 20
is used as the patient interface. The initial connection of a patient 1 to a blower and
humidifier is an obstacle to patient compliance and negates a patient's comfort and
tolerance due to the high pressure supply of gases through the cannula. Therefore, it would
be advantageous if the gases flow was slowly increased to the patient, allowing their body
time to adjust to the temperature, sensation of flow, and pressure in their nasopharynx.
This slow increase in flow may be over a considerable time, such as 30 minutes, allowing
the patient to slowly adjust to the therapy instead of feeling overwhelmed with the sudden
delivery to the nasal passage, of up to 40L/min of saturated gases.
As discussed earlier, high flows of non-humidified gases delivered to the patients
airways causes dehydration and inflammation of the airways and nasal passages. At low
flows (such as 5 litres per minute) a lower level of humidity is adequate. Because an active
pass-over humidifier 8 holds a humidification chamber 5 which contains a volume of water
6, this water has a large thermal mass and takes time to heat up enough to provide adequate
humidity at high flows.
Warm Up Mode
The blower 15 may be controlled by a controller (18 or 9) such that on start-up or
commencement of therapy by the patient 1 the flow rate of gases exiting the blower 15 is
initially supplied as a low flow.
Under the warm up mode the aim is to deliver optimal gas to the patient. To do
this, it is necessary to warm up the gases in the chamber as quickly as possible to a set
value, most preferably 37°C. As the temperature of the gases at the chamber outlet are
measured by a sensor this is the temperature that is to be controlled to the set temperature
value. In this way the patient is supplied with an optimal temperature of gases as soon as
possible. This is achieved by; turning on the heater plate 7 to full heating output, providing
a low flow of gases through the humidification chamber 5 and controlling the wall
temperature of the heated conduit 3 to avoid condensation. When the gases temperature in
the humidification chamber 5 reaches the set temperature the gases flow is increased to the
predetermined therapy flow as fast as possible, while maintaining the gases temperature in
the chamber at the set temperature. The increasing of the gases flow is performed by
controlling (increasing) the speed of the fan 21 in the blower 15. Alternatively, when the

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water chamber gases reach the set temperature the flow is increased to the target or
predetermined flow for the therapy. As soon as the gases temperature in the water
chamber recovers to approximately the set temperature, for example, 35°C, a signal is
given by the controller that the patient can now wear the interface.
As an example, gases flow is increased from the initial low flow (floWjmtiai) to a
flow that is optimal (flowopt) for the therapy being provided. It is preferred that the
maximum or optimum flow level (flowopt) is selectable by the user or care provider by way
of dial 19. In this case, the controller 18 or 9 would control the flow rate, by controlling
the fan 21 speed so that the gases flow is initially at a low flow rate of, for example, 5
L/min. Alternatively, the gases flow could be switched on for, for example, 1 to 15
seconds, at a low flow of, for example, 5 L/min to allow the temperature and humidity
readings to be taken. Then the gases flow would be switched off for a period of time, for
example, 5 to 60 seconds, to allow the humidity in the chamber to rise quicker.
Once the temperature the gases exiting the humidifier chamber reaches 37°C (the
set temperature), the flow of the gases is ramped up over a predetermined time, for
example, 30 minutes, to an optimum flow level (fiowopt) of between 15 to 40L/min, as
selected by the patient.
The above sequence of events enables the humidity in the breathing circuit to reach
the desired level as quickly as possible while minimising condensation and/or thermal
overshoot.
Drying Mode
To overcome the problem of any condensation left in the conduit 3 or in the patient
interface 20 at the end of a therapy treatment session, the breathing assistance apparatus of
the present invention provides a mode or cycle of drying out the conduit 3 and potentially
the interface 20. This is carried out by providing a turn off process that facilitates the
drying of the conduit 3 and the patient interface 20.
A drying mode is critical in minimising the risk of pathogen transport via the
conduit 3 and interface 20 to the patient 1. A drying mode also ensures there will be no
condensation left in the conduit or patient interface after a treatment session and in a next
treatment session. Condensation can cause gurgling noises and surges in airflow at the
beginning of the next humidification session making treatment uncomfortable for the
patient.

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Generally, the aim of the drying mode is to ensure the humidity of the gases in the
chamber and conduit are at or below the ambient levels the apparatus is operating in. This
is achieved by cooling the water in the humidification chamber 5, while continuing to heat
the conduit 3 and the interface 20 to a temperature that exceeds the chamber outlet gases
temperature. This is continued until the humidifier water temperature and temperature of
the gases at the chamber outlet reach or approximate room temperature. As the thermal
mass of the water in the chamber 5 exceeds the thermal mass of the plastic walls of the
conduit 3, condensation may occur if the humidifier 8 and the blower fan 21 are turned off
at the same time. To ensure this does not occur, at the end of treatment it is preferred that
the heater plate 7 is turned off but power is maintained to a heater wire 11 in the conduit 3.
The humidification means, humidifier 8, is controlled by the control means
(controller 9 or 18) at the completion of a patient's treatment. Therefore, when the patient
selects "off, a button on the apparatus, or the controller detects the end of a therapy
session, effectively only the heater plate 7 is powered down by the controller (9 or 18) and
the humidification apparatus is placed in a drying mode. During the drying mode, it is
preferred that power is maintained to the heater wire 11 and the gases supply means or
blower 15. As an example, the gases flow through the humidifier 8 and conduit 3 is a
flow, such as 20 litres per minute for a period of time, for example 15 minutes, which will
ensure the conduit has dried inside. The gases flow may be a fixed gases flow or pulses of
gases flow.
A temperature sensor 13 is preferably provided at the end of the conduit, nearest
the patient. This end of conduit temperature sensor 13 is connected to the controller 9, 18.
The end of conduit sensor 13 may be used to optimise drying of the conduit 3 by ensuring
the gases at the end of the breathing circuit are at the maximum safe operating temperature,
so that the temperature of the gases does not obtain a level that might burn a patient or
user.
Preferably it might be optimal to start at a low gases flow and then at a later stage
increase the gases flow.
In some forms of the present invention the conduit may not include a heater wire.
In this situation the controller would merely control the blower 15, such that gases and not
heat from the heater wire within the conduit alone would dry the conduit.
Deactivation of Drying Mode

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The point in time that the drying mode is deactivated may be determined by a
number of methods. The first of which is to measure the temperature of gases at the
chamber outlet 4. When the temperature of the gases at the chamber outlet 4 drops below
or equals ambient temperature (which is preferably measured by an additional temperature
sensor, for example, located at the blower 15 but connected to one of the controllers 9, 18)
the blower 15 and heater wire 11 are powered off by the controller 9, 18. In this way gases
flow through the humidification chamber 6 and as the heater plate 7 cools the humidity of
the gases flowing through the conduit 3 reduces and the conduit 3 becomes drier.
A second method for determining when the drying mode is to be deactivated by the
controller 9, 18 is to rum off the power to the humidification chamber 5 and maintain a
gases flow through the conduit 3 at a fixed speed or pulses and maintain power in the
heater wire 11 to evaporate any condensate off the walls of the conduit 3. After a
predetermined time, preferably in excess of one minute, the heater wire 11 and flow source
(blower) would be switched off.
Yet another method of controlling the drying of the conduit is to switch the gases
supply (blower) off and switch off the power to the heater plate power. The controller 9,
io wouid tiien compare tue neater plate 7 temperature witn an arnoient temperature tnat is
measured either inside or outside the humidifier or blower (as previously described).
When this temperature difference or comparison is within a predetermined limit, which
typically approximates zero, a flow of gases is caused to flow in the same manner as
described above.
It is possible that it could take longer to dry the condensate in the conduit than to
cool the chamber. In this instance it may be necessary to extend the drying mode for some
time, for example, up to 30 minutes depending on the ambient temperature of the water
remaining in the chamber.
Alternative methods of Activation of Drying Mode
It has been described that the drying mode is activated by the patient selecting or
pressing an "off' button. An alternative method of activating the drying mode is to detect
the patient 1 removing the interface 20. This may be, for example, by detecting an
increase in the flow from the blower due to decreased resistance at the patient interface at
the end of a humidification session. After a predetermined time period has elapsed, which
is long enough to ensure the patient does not put the interface back on, the drying mode is
commenced.

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As a further alternative method the time at which the patient stops breathing into
the patient interface 20 may be detected. This may be detected by monitoring for a
breathing pattern, for example using a flow sensor on the patient interface or in the blower.
Once no breathing is found and after waiting a predetermined time period the drying mode
is commenced.
In order for the apparatus to be fully powered down a user or patient must
disconnect the apparatus from the electrical power supply or for example, hold a switch or
power button down on the humidifier or blower for a period of time, for example, 5
seconds.

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CLAIMS:
1. A breathing assistance apparatus adapted to deliver humidified gases at a desired
level of humidity, flow and temperature for treatment of a patient comprising:
a) gases supply means providing a flow of gases,
b) a humidifier having a chamber adapted to receive a volume of water and a
chamber heater to heat said water in said chamber, said chamber including an inlet and an
outlet,
c) transportation pathway means to convey said humidified gases from said
humidifier to said patient,
d) a controller having stored instructions to complete the following steps at the
end of said treatment of said patient:
i) switch off power to said chamber heater,
ii) set said flow of gases from said gases supply means to a
predetermined flow for a predetermined time,
iii) after said predetermined time switch off said gases supply means.
2. A breathing assistance apparatus according to claim 1 wherein said transportation
pathway means has a pathway heater, and said apparatus further comprises:
a) an outlet temperature sensor measuring the temperature of said gases at said
outlet to said chamber,
b) a distal temperature sensor measuring the temperature of said gases at the
distal end of the transportation pathway means,
c) an ambient temperature sensor measuring ambient air temperature, and said
controller includes stored instructions to:
i) control said pathway heater over said predetermined time such that the
temperature of said gases at the distal end of said transportation pathway means, as sensed
by said second sensor does not exceed a safe temperature level, and
ii) monitor said outlet gases temperature sensor and said ambient air
temperature sensor, compare said outlet gases temperature and said ambient air
temperature and when these are substantially equal end said predetermined time and switch
of said gases supply means and said pathway heater.
3. A breathing assistance apparatus according to claim 1 wherein said transportation
pathway means has a pathway heater, and said apparatus further comprises:

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a) a distal temperature sensor measuring the temperature of said gases at the
distal end of the transportation pathway means,
b) an ambient temperature sensor measuring ambient air temperature,
c) a chamber heater temperature sensor measuring said chamber heater
temperature, and said controller includes stored instructions to:
iii) control said pathway heater over said predetermined time such that
the temperature of said gases at the distal end of said transportation pathway means, as
sensed by said second sensor does not exceed a safe temperature level, and
iv) monitor said chamber heater temperature sensor and ambient air
temperature sensor, compare said chamber heater temperature and said ambient air
temperature and when these are substantially equal end said predetermined time and switch
off said gases supply means and said pathway heater.
4. A breathing assistance apparatus according to any one of claims 1 to 3 wherein
said transportation pathway means is an extruded plastic tube, and said pathway heater is at
least two conductive wires embedded within, throughout or about the wall of said tube.
5. A breathing assistance apparatus according to any one of claims 1 to 4 wherein said
controller includes stored instructions to determine said end of said treatment when said
patient activates an "off button connected to said controller.
6. A breathing assistance apparatus according to any one of claims 1 to 4 wherein said
apparatus further comprises a patient interface sensor, and said controller includes stored
instructions to determine said end of said treatment when said patient interface sensor
detects that said patient has removed said patient interface for a predetermined period of
time.
7. A breathing assistance apparatus according to any one of claims 1 to 4 wherein said
controller includes stored instructions to determine said end of treatment when a
substantial increase of flow of gases is detected exiting said gas supply means for a
predetermined period of time.
8. A breathing assistance apparatus according to any one of claims 1 to 4 wherein said
apparatus further comprises a patient interface sensor, and said controller includes stored
instructions to determine said end of treatment when said patient interface sensor senses
that said patient's breathing through said patient interface has ceased for a predetermined
period of time.

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9. A method of controlling a breathing assistance apparatus where said apparatus is
adapted to deliver humidified gases at a desired level of humidity, flow and temperature
for treatment of a patient, said apparatus comprising a gases supply means providing a
flow of gases, a humidifier having a chamber adapted to receive a volume of water and a
chamber heater to heat said water in said chamber, transportation pathway means to
convey said humidified gases from said humidifier to said patient, and a controller that
stores a program which causes the controller at the end of said treatment of said patient to:
a) switch off power to said chamber heater,
b) set said flow of gases from said gases supply means to a predetermined flow
for a predetermined time,
c) after said predetermined time switch off said gases supply means.
10. A method of controlling a breathing assistance apparatus according to claim 9
wherein said transportation pathway means has a pathway heater, and said apparatus
further comprises an outlet temperature sensor measuring the temperature of said gases at
said outlet to said chamber, a distal temperature sensor measuring the temperature of said
gases at the distal end of the transportation pathway means, an ambient temperature sensor
measuring ambient air temperature, and said program further causes said controller to:
a) control said pathway heater over said predetermined time such that the
temperature of said gases at the distal end of said transportation pathway means, as sensed
by said second sensor does not exceed a safe temperature level, and
b) monitor said outlet gases temperature sensor and said ambient air
temperature sensor, compare said outlet gases temperature and said ambient air
temperature and when these are substantially equal end said predetermined time and switch
of said gases supply means and said pathway heater.
11. A method of controlling a breathing assistance apparatus according to claim 9
wherein said transportation pathway means has a pathway heater, and said apparatus
further comprises a distal temperature sensor measuring the temperature of said gases at
the distal end of the transportation pathway means, an ambient temperature sensor
measuring ambient air temperature, a chamber heater temperature sensor measuring said
chamber heater temperature, and said program further causes said controller to:

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a) control said pathway heater over said predetermined time such that the
temperature of said gases at the distal end of said transportation pathway means, as sensed
by said second sensor does not exceed a safe temperature level, and
b) monitor said chamber heater temperature sensor and ambient air
temperature sensor, compare said chamber heater temperature and said ambient air
temperature and when these are substantially equal end said predetermined time and switch
off said gases supply means and said pathway heater.
12. A method of controlling a breathing assistance apparatus according to any one of
claims 9 to 11 wherein said program further causes said controller to determine said end
of said treatment when said patient activates an "off button connected to said controller.
13. A method of controlling a breathing assistance apparatus according to any one of
claims 9 to 11 wherein said apparatus further comprises a patient interface sensor and said
program further causes said controller to determine said end of said treatment when said
patient interface sensor detects that said patient has removed said patient interface for a
predetermined period of time.
14. A method of controlling a breathing assistance apparatus according to any one of
claims 9 to 11 wherein said program further causes said controller to determine said end
of treatment when a substantial increase of flow of gases is detected exiting said gas supply
means for a predetermined period of time.
15. A method of controlling a breathing assistance apparatus according to any one of
claims 9 to 11 wherein said apparatus further comprises a patient interface sensor and said
program further causes said controller to determine said end of treatment when said
patient interface sensor senses that said patient's breathing through said patient interface
has ceased for a predetermined period of time.
16. A breathing assistance apparatus as herein described with reference to the
accompanying figures.
17. A method of controlling a breathing assistance apparatus as herein described with
reference to the accompanying figures.

A breathing assistance apparatus and method of controlling a breathing assistance apparatus is disclosed. Particularly, the breathing assistance apparatus is controlled such that it has a drying cycle to enable drying of the tubing that supplies
gases to a user and prevent the harbouring of pathogens within the tube. The drying cycle is preferably operated automatically by
internal controllers in the apparatus. However, it may be manually activated by pressing a button on the apparatus. The drying cycle
is preferably activated at the end of a user's treatment session.