WO2019200459A1 - Liquid ventilator and method to induce tidal liquid ventilation and/or hyporthermia - Google Patents

Liquid ventilator and method to induce tidal liquid ventilation and/or hyporthermia Download PDF

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Publication number
WO2019200459A1
WO2019200459A1 PCT/CA2019/050450 CA2019050450W WO2019200459A1 WO 2019200459 A1 WO2019200459 A1 WO 2019200459A1 CA 2019050450 W CA2019050450 W CA 2019050450W WO 2019200459 A1 WO2019200459 A1 WO 2019200459A1
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WO
WIPO (PCT)
Prior art keywords
liquid
breathable liquid
cooling
mammal
oxygenator
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/CA2019/050450
Other languages
English (en)
French (fr)
Inventor
Philippe Micheau
Renaud Tissier
Matthias KOHLHAUER
Julien MOUSSEAU
Mathieu NADEAU
Jonathan VANDAMME
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Universite de Sherbrooke
Institut National de la Sante et de la Recherche Medicale INSERM
Ecole Nationale Veterinaire dAlfort
Universite Paris Est Creteil Val de Marne
Universite de Marne la Vallee
Original Assignee
Universite de Sherbrooke
Institut National de la Sante et de la Recherche Medicale INSERM
Ecole Nationale Veterinaire dAlfort
Universite Paris Est Creteil Val de Marne
Universite de Marne la Vallee
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Universite de Sherbrooke, Institut National de la Sante et de la Recherche Medicale INSERM, Ecole Nationale Veterinaire dAlfort, Universite Paris Est Creteil Val de Marne, Universite de Marne la Vallee filed Critical Universite de Sherbrooke
Priority to EP19789212.8A priority Critical patent/EP3781241B1/en
Priority to KR1020207032986A priority patent/KR102774314B1/ko
Priority to CA3097435A priority patent/CA3097435A1/en
Priority to CN201980040240.5A priority patent/CN112770800B/zh
Priority to JP2021506017A priority patent/JP7386843B2/ja
Priority to US17/048,263 priority patent/US12083271B2/en
Publication of WO2019200459A1 publication Critical patent/WO2019200459A1/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/0054—Liquid ventilation
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    • A61F7/00—Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F7/0085—Devices for generating hot or cold treatment fluids
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    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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Definitions

  • the present invention relates to the field of artificial ventilators and, more particularly, to airway pressure and lung temperature.
  • TLV Total liquid ventilation
  • PFC perfluorocarbon
  • a first aspect of the present invention is directed to a ventilator for liquid ventilation of a mammal comprising: ventilator for liquid ventilation of a mammal comprising:
  • a respiratory circuit defining an inspiratory circuit and an expiratory circuit, and comprising:
  • a pumping assembly operatively connected to the oxygenator for pumping the breathable liquid in and out of the mammal’ s lungs through the respiratory circuit;
  • a pressure sensor operatively connected to the respiratory circuit and configured to measure a pressure of a respiratory flow of the breathable liquid
  • control unit operatively connected to the pressure sensor and the pumping assembly for controllably exchanging the breathable liquid between the oxygenator and the mammal’s lungs while controlling the expiratory flow of the breathable liquid pumped out of the lungs;
  • control unit comprises a processor for:
  • a pressure P calculated from the measured pressure; and when the pressure P reaches a negative threshold indicating a collapse of the mammal’s trachea, reducing in real-time the expiratory flow of the breathable liquid according to a factor R while pumping the breathable liquid out of the lungs during a given expiratory period of time in order to maintain a targeted end-expiratory breathable liquid volume, or EEBLV, in the mammal’s lungs.
  • EEBLV end-expiratory breathable liquid volume
  • the targeted EEBLV is between 10 and 20 ml/Kg for a respiratory frequency of between 2 and 8 rpm and a tidal volume of breathable liquid of between 4 to 10 mL/Kg.
  • the negative threshold of the pressure P is equal or inferior to about -50 cmPhO and the given expiratory period of time during which the pumping assembly pumps the breathable liquid out of the lungs allows removing at least 80% of the targeted tidal expiratory volume of the breathable liquid.
  • the ventilator further comprises a reservoir located at a level below the mammal and fluidly connected to the pumping assembly, wherein the control unit is further configured to open in real-time the respiratory circuit when the pressure P reaches a critical pressure inferior to about -130 cmfhO or superior to about +130 cmfhO in order to generate a low negative pressure P (such as a negative pressure P close to 0 cmPhO) to drain the breathable liquid from the lungs by gravity towards the reservoir.
  • a critical pressure inferior to about -130 cmfhO or superior to about +130 cmfhO in order to generate a low negative pressure P (such as a negative pressure P close to 0 cmPhO) to drain the breathable liquid from the lungs by gravity towards the reservoir.
  • the ventilator further comprises an alarm unit operatively connected to the control unit for triggering an alarm when the critical pressure is reached.
  • the pressure of the respiratory flow is measured at the mouth of the mammal.
  • the pumping assembly comprises:
  • a Y connector comprising a junction for connecting the pumping assembly to a proximal end of an endotracheal tube having a distal end insertable in the mammal’s trachea;
  • an expiratory pump fluidly connected to the junction of the Y connector and upstream to the oxygenator;
  • an inspiratory pump fluidly connected to the junction of the Y connector and downstream to the oxygenator ;
  • valves each valve being independently controlled by the control unit for driving the breathable liquid going through the expiratory and inspiratory pumps and guiding the breathable liquid to the lungs.
  • the ventilator further comprises a cooling unit fluidly connected to the oxygenator, the cooling unit producing a cooling fluid at a cooling temperature for cooling and/or maintaining an inspiratory temperature of the breathable liquid going through the oxygenator before being driven to the mammal’s lungs.
  • the cooling unit is in fluid communication with the oxygenator for receiving the cooling fluid therefrom, the cooling fluid being then cooled while going through the cooling unit; the ventilator further comprising a pump in fluid communication with the cooling unit and the oxygenator for pumping back the cooling fluid from the cooling unit to the oxygenator where the cooling fluid thermally exchanges with the breathable liquid of the ventilator circulating in the oxygenator for cooling the breathable liquid before the re-instillation of the breathable liquid into the mammal’s lung.
  • the ventilator further comprises a temperature sensor for measuring an expiratory temperature of the breathable liquid pumped out of the mammal’s lungs, the temperature sensor being operatively connected to the control unit, the control unit being further configured to adjust the cooling temperature of the cooling fluid by controlling the pump and therefore controlling a flow of cooling fluid going through the cooling unit and the oxygenator in order to adjust the temperature of the breathable liquid in function of the measured expiratory temperature.
  • controlling the pump consists in turning on the pump during a first pre-set period of time and turning off the pump during a first pre-set period of time to control the flow of cooling liquid.
  • a second aspect of the present invention is directed to the use of a targeted end- expiratory breathable liquid volume, or EEBLV, of a breathable liquid inferior to a functional residual capacity, or FRC, of the lungs of a mammal for preventing deleterious effects on the mammal’s lungs during a liquid ventilation of said mammal.
  • EEBLV is between 10 and 20 ml/Kg for a respiratory frequency of between 2 and 8 rpm and a tidal volume of the breathable liquid of 4 to 10 mL/Kg.
  • a third aspect of the present invention is directed to a method for liquid ventilation of a mammal comprising the steps of:
  • the EEBLV in the method is between 10 and 20 ml/Kg for a respiratory frequency of between 2 and 8 rpm and a tidal volume of breathable liquid of between 4 and 10 mL/Kg.
  • the negative threshold of the pressure P is equal or inferior to about -50 cmfhO, and wherein the given expiratory period of time during which the breathable liquid is pumped out of the lungs allows removing at least 80% of the volume of the breathable liquid.
  • the method further comprises the step of evacuating the breathable liquid from the mammal’s lungs when the pressure P is a critical value inferior to about -130 cmEhO or superior to about +130 cmEhO.
  • the method further comprises the step of triggering an alarm when the critical value is reached.
  • the method further comprises the step of cooling and/or maintaining a temperature of the breathable liquid while pumping the breathable liquid in and out of the lungs of the mammal.
  • the step of cooling and/or maintaining the temperature of the breathable liquid comprises: producing a cooling fluid, and thermally exchanging the cooling fluid with the breathable liquid for cooling the breathable liquid before re-instilling the breathable liquid into the mammal’s lung.
  • the method further comprises the steps of: measuring an expiratory temperature of the breathable liquid pumped out of the mammal’s lungs; and adjusting a temperature of the cooling fluid in function of the measured expiratory temperature for adjusting the temperature of the breathable liquid pumped into the lungs.
  • the step of adjusting the temperature of the cooling fluid consists in maintaining a flow of the cooling fluid during a first pre-set period of time, or stopping said flow during a second pre-set period of time, when the cooling fluid thermally exchanges with the breathable liquid.
  • a fourth aspect of the present invention is directed to an apparatus for safe induction of hypothermia during liquid ventilation of a mammal, the apparatus comprising:
  • a cooling unit configured to produce a cooling fluid at a cooling temperature when the cooling fluid circulates through the cooling unit, the cooling unit being in fluid communication with an oxygenator of a liquid ventilator for receiving the cooling fluid therefrom;
  • controllable pumping unit in fluid communication with the oxygenator and the cooling unit, the controllable pumping unit being configured to pump back the cooling fluid from the cooling unit to the oxygenator module where the cooling fluid thermally exchanges with a breathable liquid of the liquid ventilator circulating in the oxygenator module for controlling an inspiratory temperature of the breathable liquid oxygenated by the oxygenator before the re-instillation of the cooled oxygenated breathable liquid into the mammal’s lung;
  • the liquid ventilator comprises a temperature sensor for measuring in real-time an expiratory temperature of the breathable liquid pumped out of the mammal’s lungs, the temperature sensor being operatively connected to the controllable pumping unit to modify a flow of the cooling fluid and therefore to adjust the inspiratory temperature of the breathable liquid in function of the measured expiratory temperature.
  • control of the pumping unit consists in turning on the pumping unit during a first pre-set period of time and turning off the pumping unit during a second pre-set period of time to control the flow of cooling liquid going through the cooling unit and the oxygenator.
  • the pumping unit is configured to pump the cooling fluid at a controlled mass flow rate in order to control a cooling power of the thermal exchange in the oxygenator.
  • the pump is operatively connected to a processor module of the liquid ventilator configured to control the mass flow rate of the cooling fluid and as such to vary the temperature of the breathable liquid in the oxygenator.
  • the cooling fluid may comprise water.
  • a fourth aspect of the present invention is directed to a method for induction of hypothermia in a mammal comprising the steps of:
  • step d) adjusting in real-time the inspiratory temperature of the breathable liquid in function of the expiratory temperature measured in step c) by modifying a flow of the cooling fluid circulating through the cooling unit and the oxygenator.
  • modifying the flow of the cooling fluid circulating through the cooling unit and the oxygenator consists in circulating the cooling fluid during a first pre-set period of time and stopping the circulation of the cooling liquid during a second pre-set period of time.
  • the method further comprises the step of varying a mass flow rate of the cooling liquid circulating into the oxygenator for controlling a cooling power of the thermal exchange in the oxygenator.
  • the method further comprises the step of varying the temperature of the breathable liquid circulating in the oxygenator by varying the mass flow rate of the cooling liquid circulating in the cooling unit.
  • the cooling fluid comprises water.
  • the breathable liquid may preferably comprises perflurocarbons, or PFC, and the mammal is preferably a human.
  • Figure 1 is a schematic illustration of a liquid ventilator according to an embodiment of the present invention.
  • Figure 2 is diagram illustrating a ventilator according to another embodiment of the present invention
  • Figure 3 is a schematic representation of the liquid ventilator according to an embodiment of the present invention connected to a patient function during inspiration phase;
  • Figure 4 is a schematic representation of the liquid ventilator according to an embodiment of the present invention connected to a patient function expiration phase;
  • Figure 5 is a schematic illustration of an up-scaled liquid ventilator according to another embodiment of the present invention.
  • Figures 6A and 6B show a three-dimensional illustration of the ventilator according to an embodiment of the present invention
  • Figure 7 illustrates an apparatus for safe induction of hypothermia during liquid ventilation of a mammal according to an embodiment of the present invention
  • Figure 8 illustrates the working of the pumping assembly of the apparatus illustrated on Figure 7 with (A) the algorithm and (B) an example temperature control of the expiratory flow by controlling the pumping unit
  • Figure 9 illustrates an experimental protocol according to an embodiment of the present invention including five groups of piglets submitted to 30 min of TLV with different tidal volumes (TV of 8 or 16 ml/kg) and end-expiratory volumes (EEBLV of 15 or 30 ml/kg), as compared to Sham animals with conventional mechanical ventilation only, the four corresponding groups are so-called TVs-EVu, TVie-EVis, TV8-EV30 and TV16-EV30, respectively;
  • Figure 10 shows typical perfluocarbon flow (upper raw), pressure at mouth and pulmonary volume of perfluocarbon during the first 5 min of total liquid ventilation (TLV) in a 63 kg pig;
  • Figure 11 is a schematic representation of experimental protocol in large pigs submitted to 30 min of hypothermic TLV followed by conventional gaseous ventilation and rewarming, before awakening. Animals were followed during 10 days before euthanasia for post-mortem analyses;
  • Figure 12 shows body temperatures in the different compartments during the TLV episode, showing a rapid decrease of target temperature (32-33°C) within 20 min in all compartments;
  • Figure 13 shows blood pH, and carbon dioxide and oxygen partial pressure (pC0 2 and pO 3 ⁇ 4 respectively);
  • Figure 14 shows thoracic computerized tomography (CT-scan) of an explanted lung in a pig at the end of the follow-up. No macroscopic foci of perfluorocarbons can be observed, suggesting complete elimination;
  • Figure 15 shows respiratory cycles measurements in application of the method according to an embodiment of the present invention when a collapses phenomenon occurs: (A) pressure (cmH 2 0), (B) flow (mL/s), (C) frequency F (bpm), (D) EEBLV (mL); [0053] Figure 16 shows normal flow and volume of breathable liquid in function of time versus when an airway collapse phenomenon occurs;
  • Figure 17 shows a detailed perspective view of a Y-connector according to an embodiment of the present invention ;
  • Figure 18 shows the measure of EEBLV, inspired volume and expired volume during the liquid ventilation of a pig;;
  • Figure 19 shows signals measured on a pig during one hour of liquid ventilation (A) and the same signals during one minute from the time 2.3 minutes of the liquid ventilation (B);
  • Figure 20 shows the same signals as for Figure 19 measured on a pig during one hour of liquid ventilation (A) and the same signals during one minute from the time 40.55 minutes of the liquid ventilation (B);
  • Figure 21 is a sequence diagram showing operations of an exemplary method for liquid ventilation of a mammal according to an embodiment of the present invention.
  • Figure 22 is another sequence diagram showing operations of an exemplary method for liquid ventilation of a mammal according to an embodiment of the present invention.
  • Figure 23 is a sequence diagram showing operations of an exemplary method for safe induction of hypothermia during liquid ventilation of a mammal according to an embodiment of the present invention
  • TLV total liquid ventilation
  • a new apparatus has been developed that can continuously regulate expiratory flow as well as PFC volumes and pressures, which was a great cornerstone for TLV translation. At this step, precise recommendations are still needed to provide an efficient procedure, regarding targeted PFC volumes, filling pressures and PFC target temperatures.
  • the invention consists in integrating the concept of TLV using liquid volumes below FRC using a new liquid ventilator. Beyond the automatization of the whole process, the technology has been up-scald to confirm that TLV at residual volumes below FRC can provide a safe procedure while enabling the full potential of TLV in a mammal such as humans or adult-sized animals. Such tidal liquid ventilation strongly differs from the previously known TLV approach, opening promising perspectives for a safer clinical translation.
  • a liquid ventilator in accordance with preferred embodiment of the invention are illustrated on Figures 1 to 6.
  • the ventilator (100) for liquid ventilation of a mammal comprises a liquid circuit forming a loop, and including first a reservoir (110) configured to contain a breathable liquid (BL), and an oxygenator (120) fluidly connected to the reservoir (110) for oxygenating the breathable liquid.
  • a reservoir (110) configured to contain a breathable liquid (BL)
  • an oxygenator (120) fluidly connected to the reservoir (110) for oxygenating the breathable liquid.
  • the reservoir (110) and the oxygenator (120) may alternatively form a unique assembly where the reservoir is integrated into the oxygenator. In another embodiment, there is no reservoir (not illustrated).
  • the ventilator (100) as shown on Figures 6A and 6B may have a pair of pockets suspended in a upper section of the ventilator for containing the BL that will be distributed into the ventilator at the beginning of the ventilation process. Also, the ventilator is supported by a frame (112) that can be moved thanks to a plurality of wheels (134). The ventilator may also have a first scale (114) located under the reservoir (110) and/or a second scale (114) located under the oxygenator (120). The scales are operatively connected to the control unit (180) in order to determine in real-time the amount of BL contained in the reservoir and/or the oxygenator and to calculate therefore the volume of BL in the mammal’s lungs.
  • the oxygenator is configured to receive a mixture of air (122) and dioxygen - O2 gas (124) pre-mixed in a gas blender (126).
  • the ventilator may also comprise a gas condenser (128) typically located above the reservoir, or adjacent a top section of the oxygenator, for condensing the breathable liquid (BL) and limits its loss.
  • the ventilator (100) may optionally comprises a filtering unit (130) upstream the oxygenator for filtering the breathable liquid (BL) before entering the oxygenator. Reservoirs, oxygenators, gas blender, filters, tubing and condenser such as those known in the art of TLV technology can be used in connection with the present invention.
  • the ventilator (100) also comprises a pumping assembly (140) operatively connected to the reservoir (110) and the oxygenator (120) for pumping the breathable liquid (BL).
  • the pumping assembly may comprise a Y connector (300) comprising a junction for connecting the pumps to a proximal end (152) of an endotracheal tube (150) having a distal end (154) insertable in the mammal’s trachea (156).
  • the pumping assembly (140) comprises a first expiratory pump (144) fluidly connected to the Y connector (300) for pumping the breathable liquid out of the lungs (158) toward the filter (130) and then the oxygenator (120) before reaching the optional reservoir (110) where a reserve of oxygenated breathable liquid may be stored.
  • the pump assembly (140) then also comprises an inspiratory pump (146) fluidly connected to the reservoir (110) for injecting the oxygenated breathable liquid pre-stored in the reservoir into the lungs through the Y connector (150) closing as such the loop circuit of the ventilator.
  • the pumping assembly further comprises a plurality of valves (148), typically four valves (l48a, l48b, l48c, l48d), which in connection with the two pumps (144, 146), the tubes and Y connector, allow driving the breathable liquid (BL) going through the expiratory and inspiratory pumps and guiding the breathable liquid to the lungs.
  • a plurality of valves typically four valves (l48a, l48b, l48c, l48d), which in connection with the two pumps (144, 146), the tubes and Y connector, allow driving the breathable liquid (BL) going through the expiratory and inspiratory pumps and guiding the breathable liquid to the lungs.
  • oxygenator V res perfluorocarbon volume in the oxygenator, T res perfluorocarbon temperature in the oxygenator
  • the ventilator (100) is connected to the patient via the Y-connector (300).
  • the four pinch valves (148a, 148b, 148c, 148d) are programmed to guide the liquid flow (BL) to the lungs (158).
  • the valves (148b) and (148d) are open and the valves (148a) and (148c) are closed.
  • the inspiratory pump (146) inserts the respiratory PFC (BL) through the endotracheal tube (150) to the lungs (158). Hence the liquid arrives directly to the lung (158) from the reservoir (110) at the controlled temperature T res .
  • the expiratory pump (144) returns a tidal volume of liquid (previously expired from the lung (158)) to the oxygenator (120).
  • the valves (l48b) and (l48d) are closed, and the valves (l48a) and (l48c) are open.
  • the expiratory pump (144) withdraws the liquid (e.g. PFC) through the endotracheal tube (150) from the lungs (158).
  • the inspiratory pump (146) is filled with a tidal volume of liquid (BL) pumped from the reservoir (110).
  • the liquid temperature that directly arrives from the lung (158) is measured at the patient connector location (300).
  • this temperature measurement at the Y-connector (300) can be used to calculate an indirect measurement of the lung temperature TL, as detailed and explained in international patent application no. WO 2014/205548 Al (Nadeau et al), published on December 31, 2014, the content of which is incorporated herein by reference.
  • the function of the oxygenator (120) is to oxygenate the liquid (BL) and to control its temperature. Dioxygen (O2) and carbon dioxide (CO2) concentrations in the PFOB is monitored and controlled by the gas mixer (See 126, Fig. 1). Water flowing within the double walls of the oxygenator (120) is used for cooling the liquid (e.g. PFC) inside the oxygenator before its re instillation into the lungs.
  • a cooling fluid such as one comprising cold water
  • CF cooling fluid
  • a cooling system 200
  • the oxygenator 120
  • a pump 210
  • the command u of the pump allows controlling the cooling power (CP) of the thermal exchange in the oxygenator (120).
  • CP cooling power
  • CP cooling power
  • u 0.
  • the maximal cooling power is applied to the oxygenator.
  • the liquid ventilator is designed to initiate liquid ventilation with a breathable liquid (e.g. PFC) at a controlled hospital room temperature (e.g.
  • the output variable is the lung temperature TL.
  • the ventilator (100) also comprises a pressure sensor (160) operatively connected to the respiratory circuit and configured to measure a pressure of a respiratory flow of the breathable liquid.
  • the pressure sensor can measure the pressure at the mouth of the patient.
  • the pressure sensor can be located inside the Y-connector (300) together with a temperature sensor.
  • FIG 17 is a detailed perspective view of a Y-connector in accordance of a preferred embodiment of the invention.
  • the Y-connector (300) comprises an inspiratory liquid port (310) for receiving the breathable liquid (BL), e.g. PFC, from the reservoir (110) and/or the oxygenator (120), an expiratory liquid port (320) for returning the BL to the oxygenator (120), an endotracheal tube port (330), ETT port, for connection of the endotracheal tube ETT (150), aBL temperature sensor (340), and avalve (350), such as arotary valve, allowing an user to select TLV by connecting the liquid ports (310) and (320), to the ETT port (330).
  • BL breathable liquid
  • PFC e.g. PFC
  • the rotary valve (350) is mechanically connected to a rotation sensor (360) in order to measure the state of the rotary valve (350).
  • the ETT port (330) comprises a first parietal pressure sensor (370) to measure the parietal pressure P of the flow in the ETT port.
  • a second measure of the parietal pressure can be obtained with a second pressure sensor (372) located in front of the first parietal pressure sensor (370).
  • the temperature sensor (340) is connected to the Y-connector via different connecting ports, either located in the expiratory circuit (380a), the inspiratory circuit (380b, as represented on the figure 17), or connected to both the inspiratory and expiratory circuits (380c).
  • the BL temperature sensor (340) and the parietal pressure sensors (370, 372) are operably connected to the ventilator control unit VCU (180).
  • the ventilator further comprises a control unit (180) operatively connected to the pressure sensor (160) and the different elements of the pumping assembly (140) for controllably exchanging the breathable liquid between the oxygenator and the mammal’s lungs while controlling the expiratory flow of the breathable liquid pumped out of the lungs.
  • the control unit (180) comprises a processor (182) for effecting in real-time a pressure P calculated from the measured pressure, e.g. at the mouth of the mammal or patient.
  • the processor (182) allows reducing in real-time the expiratory flow of the breathable liquid according to a factor R while pumping the breathable liquid out of the lungs during a given expiratory period of time in order to maintain a targeted end-expiratory breathable liquid volume, or EEBLV, in the mammal’s lungs.
  • the negative threshold of the pressure P is equal or inferior to about -50 cmFhO and the given expiratory period of time during which the pumping assembly pumps the breathable liquid out of the lungs allows removing at least 80% of the targeted tidal expiratory volume of the breathable liquid.
  • the EEBLV is typically between 10 and 20 ml/Kg for a respiratory frequency of between 2 and 8 bpm (breath per minute), preferably 4 to 6 bpm, and a tidal volume of breathable liquid of between 4 to 10 mL/Kg. More details are presented in the examples of the present description.
  • the control unit (180) is a computer equipped with a processor (182), a graphic user interface or GUI (184) for entering data and displaying measurements, traces and results, and a ventilator control unit in real-time or VCU (186). Pumps, valves and sensors of the ventilator are operatively connected to the processor.
  • the reservoir (110) of the ventilator as illustrated on Figures 6A is fluidly connected to the pumping assembly, and is preferably located at a level below the mammal or patient to take advantage of the gravitational force or gravity. Reference can be made to the table or surface on which the mammal or human is laid on during the ventilation procedure.
  • the control unit (180) may be then further configured to open in real-time the pumping the respiratory circuit when the pressure P reaches a critical pressure inferior to about -130 cmEhO or superior to about +130 cmEhO. When the circuit is opened, the breathable liquid can be evacuated from the lungs by gravity towards the reservoir (110).
  • the ventilator may then further comprise an alarm unit (190) operatively connected to the control unit for triggering an alarm when the critical pressure is calculated by the processor of the control unit.
  • the ventilator (100) may further comprise a cooling unit (200) operatively connected to the oxygenator (120) for cooling and/or maintaining a temperature of the breathable liquid going through the oxygenator before being driven to the reservoir and going through the pumping assembly and mammal’s lungs.
  • a cooling unit (200) can be a container or bath 210 having a upper access door 212 to allow pouring water into the container.
  • the cooling unit can be controlled by a bath control system 214, preferably operatively connected to the control unit of the ventilator, as better explained herein after.
  • the present invention is directed to method (1000) for liquid ventilation of a mammal comprising the steps of:
  • the EEBLV is between 10 and 20 ml/Kg for a respiratory frequency of between 2 and 8 rpm and a tidal volume of breathable liquid of between 4 and 10 mL/Kg.
  • the negative threshold of the pressure P is equal or inferior to about -50 cmEhO (1350), and the given expiratory period of time during which the breathable liquid is pumped out of the lungs allows removing at least 80% of the tidal volume of the breathable liquid.
  • the method (1000) further comprises the step of evacuating the breathable liquid from the mammal’s lungs (1500) when the pressure P is a critical value inferior to about -130 cmFhO (1360) or superior to about +130 cmFhO (1370.
  • the method may further comprises the step of triggering an alarm when the critical value is reached.
  • the method (1000) further comprises the step of cooling and/or maintaining a temperature of the breathable liquid while pumping the breathable liquid in and out of the lungs of the mammal.
  • the step of cooling and/or maintaining the temperature of the breathable liquid comprises:
  • the method (1000) further comprising the steps of:
  • the step of adjusting the temperature of the cooling fluid consists in maintaining a flow of the cooling fluid during a first pre-set period of time, or stopping said flow during a second pre-set period of time, when the cooling fluid thermally exchanges with the breathable liquid.
  • Figure 2 schematically represents the different components of a ventilator equipped with a cooling unit in accordance with a preferred embodiment of the invention, and in which:
  • GUI Graphic user interface for entering data and displaying measurements, traces and results
  • VCU ventilator control unit in real-time
  • another aspect of the present invention is directed to an apparatus for safe induction of hypothermia during liquid ventilation of a mammal, e.g. a human.
  • the apparatus (200) comprising a cooling unit (210) configured to produce a cooling fluid (CF) at a cooling temperature when the cooling fluid circulates through the cooling unit.
  • the cooling fluid may comprise water, preferably cold water at a temperature, preferably between - 10 °C and +20 °C, and all values in between.
  • the cooling unit being in fluid communication (216) with an oxygenator (120) of a liquid ventilator (100) for receiving the cooling fluid therefrom (216).
  • the apparatus also comprises a controllable pumping unit (230) in fluid communication with the oxygenator (120) and the cooling unit (210).
  • the controllable pumping unit (230) is configured to pump back the cooling fluid (CF) from the cooling unit to the oxygenator module (120) where the cooling fluid (CF) thermally exchanges (240) with a breathable liquid (BL) of the liquid ventilator (100) circulating in the oxygenator module for controlling an inspiratory temperature of the breathable liquid oxygenated by the oxygenator before the re-instillation of the cooled oxygenated breathable liquid into the mammal’s lung.
  • the breathable liquid typically comprises perflurocarbons, or PFC.
  • the liquid ventilator (100) comprises a temperature sensor (260) for measuring in real-time an expiratory temperature of the breathable liquid pumped out of the mammal’s lungs, the temperature sensor being operatively connected to the controllable pumping unit (230) to modify a flow of the cooling fluid and therefore to adjust the inspiratory temperature of the breathable liquid in function of the measured expiratory temperature.
  • Figure 8(A) is an example of algorithm for the control of the pumping unit (230), which consists in turning on the pumping unit during a first pre-set period of time, e.g. 20 sec., and turning off the pumping unit during a second pre-set period of time, e.g. 30 sec., to control the flow of cooling liquid going through the cooling unit and the oxygenator.
  • Figure 8(B) is an example of how the control unit controls the pumping assembly to reach and maintain a target temperature of the expiratory flow around 31 °C.
  • the pumping unit can be configured to pump the cooling fluid at a controlled mass flow rate in order to control a cooling power of the thermal exchange in the oxygenator.
  • the pump is then operatively connected to a processor module of the liquid ventilator configured to control the mass flow rate of the cooling fluid and as such to vary the temperature of the breathable liquid in the oxygenator.
  • a method for induction of hypothermia in a mammal, such as a human, is illustrated on Figure 23.
  • the method (2000) comprises the steps of:
  • a breathable liquid e.g. PFC
  • step d) adjusting in real-time the inspiratory temperature of the breathable liquid in function of the expiratory temperature measured in step c) (2300) by modifying a flow of the cooling fluid circulating through the cooling unit and the oxygenator (2400).
  • the step of modifying the flow of the cooling fluid circulating through the cooling unit and the oxygenator (2400) consists in circulating the cooling fluid during a first pre-set period of time, e.g. 20 s, and stopping the circulation of the cooling liquid during a second pre-set period of time, e.g. 30 s, as illustrated on Figure 8.
  • the method may further comprise the step of varying a mass flow rate of the cooling liquid circulating into the oxygenator for controlling a cooling power of the thermal exchange in the oxygenator.
  • the method (2000) then further comprises the step of varying the temperature of the breathable liquid circulating in the oxygenator by varying the mass flow rate of the cooling liquid circulating in the cooling unit. Examples:
  • lung volume has been assessed by chest computerized tomography (CT-scan) in four anesthetized piglets.
  • PEEP 0 and 5 cmEhO
  • TLV was induced with perfluoctylbromide (PFOB) TLV.
  • PFOB perfluoctylbromide
  • Fig. 9 the evaluation of the two selected EEBLV levels was crossed with two different levels of tidal volume (TV) set at either 8 or 16 ml/kg (TVs-EVis, TVie-EVis, TVs- EV30, TV16-EV30 groups, respectively).
  • Total (or tidal) liquid ventilation necessitates a dedicated mechanical system in order to ventilate completely filled lungs with a tidal volume of breathable liquid (BL).
  • the liquid ventilator inserts and withdraws the tidal volume V t of BL from the lungs in order to ensure that the amount of breathable liquid in the lungs at the end of expiration phase (EEBLV) is closed to the targeted EEBLV specified by the clinician.
  • the measurement of EEBLV can be obtained by monitoring the patient’s weight, end-expiratory pressure or liquid volume in the ventilator.
  • the volume of BL in the oxygenator may be measured using a scale (114) (see Fig.
  • the ventilator control unit VCU
  • Vprim the primary volume of BL
  • Vprim the initial volume of BL in the liquid ventilator before the TLV
  • the control unit module computes the EEBLV correction, ⁇ V
  • the requested correction of EEBLV, AV[k ⁇ , is the BL volume to retrieve from (if negative) or to add into (if positive) the lungs during one cycle.
  • the targeted inspiratory and expiratory volume is computed with the targeted tidal volume, Vt[k ⁇ , and the requested correction A V[k ⁇ .
  • Figure 18 shows as an example the measurements of the EEBLV (mL), the inspiratory volume Vinspi (mL) and the expiratory volume Vexpi(mL) during the ventilation of a pig (80kg) from the time 17 minutes (l050s) for 14.5 minutes:
  • the EEBLV is estimated from the amount of liquid in the reservoir.
  • the Modification of EEBLVref by the user the user modify the value the EEBLVref in order to increase EEBLV from 10 mL/Kg to 15 mL/Kg (800 mL to 1200 mL) and after, the user decreases the EEBLVref from 15 mL/Kg to 10 mL/Kg.
  • Figures 15 and 16 provides respiratory cycles data when a collapse of the trachea occurs.
  • Figure 15 shows an experiment with a pig of 73 Kg, using the up-scaled ventilator ( Figures 5 and 6) during 60 s from the time 1450 s.
  • the dashed line of pressure (Fig. 15 A) corresponds to the limit of collapse at -250 cmFhO
  • the dashed line of frequency (Fig. 15C) shows the targeted frequency at 6 bpm
  • the dashed line of EEBLV Fig. 15D) shows the targeted EELV at 800 mL.
  • EEBLV 800 mL/Kg (10.9 mL/Kg) (Fig.
  • the expiratory time is not modified and the expiratory flow profile is reduced by a ratio equal to RatioCC. Moreover, once the airway collapse is detected, an alarm is activated to warn the operator that the ventilation parameters need to be adapted in order to prevent the airway collapse phenomenon on the next expiration.
  • Figures 19 and 20 shows signals measured during one hour of liquid ventilation (A) on a pig (60-80 kg) using the up-scaled ventilator ( Figures 5 and 6) and the same signals during one minute from the time 138 seconds (or 2.3 minutes) of the liquid ventilation (Fig. 19B) and during one minute from the time 2433 seconds (or 40.55 minutes) of the liquid ventilation.
  • Pressure in cmFhO (Fig. 19B and 20B) with plain line : pressure measured at the Y connector and dashed line : limit collapse set at different values.
  • Instantaneous frequency F in breath per minute or bpm
  • Fig. 19C and 20C with plain line : F realized by the liquid ventilator, and dashed line : F desired frequency is set by the user.
  • Figure 19B show the same signals during one minute from the time 2.3 minutes of the liquid ventilation.
  • the dashed line of pressure corresponds to the limit of collapse set at -250 cmFhO, and the dashed line shows the desired frequency is set at 6 bpm. From 0 to 24 (s) : normal liquid ventilation 3 cycles without collapse. The measured frequency (F) is equal to the desired frequency set at 6 bpm (cycle of 10 s).
  • the expiratory profile allows to avoid the collapse, because the pressure measured at the Y-connector is below -250 cmFhO. The expiratory time is 7 s. The inspiratory time is 3 s. From 24 s to 60 s : 3 collapus are detected.
  • the pressure measured at the Y-connector is below -250 cmFhO (value set by the operator).
  • the expiratory flow is automatically decreased from -140 mL/s to -70 mL/s and the expiratory time is increased to 1 ls. So, the estimated instantaneous frequency decreases from 6 bpm to 4 bpm (at time 34 s).
  • Figure 20 shows signals measured during one minute from the time 40.55 minutes of the liquid ventilation. From 0 to 30 (s) : collapus are detected. At these moments, the pressure measured at the Y-connector is below -250 crrdHO (value set by the operator). At 4.2 s, the expiratory flow is automatically decreased from -120 mL/s to -60 mL/s and the expiratory time is increased to 1 ls. So, the estimated instantaneous frequency is 4 bpm instead of the target 6 bpm. From 30 s: normal liquid ventilation without collapse because the pressure measured at the Y-connector is below -250 cmFhO. The expiratory time is 7 s. The inspiratory time is 3 s. So, the measured frequency (F) is equal to the desired frequency set at 6 bpm (cycle of 10 s).
  • Pulmonary gas exchanges was not modified during TLV as compared to conventional mechanical ventilation, as shown by arterial blood pH and partial pressure of 0 2 and CO2 (Fig. 13).
  • blood oxygen saturation remained above 97-98% in all animals from the first day after TLV to the end of the follow-up, showing a long-term pulmonary tolerance of the procedure.
  • CT-scan imaging of explanted lungs did not show any visible macroscopic foci of PFC residues since the entire lung parenchyma was diffusely hypoattenuating.
  • a new approach for TLV through incomplete lung filling with PFC below FRC and subsequent tidal liquid ventilation is disclosed. This represents a radical paradigm shift as compared to previous beliefs, that considered that lungs should be primarily completely filled with PFC and fully degassed since the filling phase.
  • This lung-conservative approach of TLV was further automatized with an up-scaled device for large animals continuously controlling EEBLV below FRC ranges. Partial liquid ventilation was tested in humans but the largest trial raised skepticism regarding the actual safety of this procedure. Those negative results were poorly deciphered a posteriori and it was often overstated that any way of liquid ventilation enhanced trauma risks by itself, regardless its exact way of induction.
  • the disclosed methods, ventilators and apparatus for inducing hypothermia may be customized to offer valuable solutions to existing needs and problems of related to the lack of maturity of current liquid ventilation technology.
  • Various network links may be implicitly or explicitly used in the context of the present invention. While a link may be depicted as a wireless link, it could also be embodied as a wired link using a coaxial cable, an optical fiber, a category 5 cable, and the like. A wired or wireless access point (not shown) may be present on the link between. Likewise, any number of routers (not shown) may be present and part of the link, which may further pass through the Internet.
  • the present invention is not affected by the way the different modules exchange information between them.
  • the memory module and the processor module of the control unit could be connected by a parallel bus, but could also be connected by a serial connection or involve an intermediate module (not shown) without affecting the teachings of the present invention.
  • a method is generally conceived to be a self-consistent sequence of steps leading to a desired result. These steps require physical manipulations of physical quantities. Usually, though not necessarily, these quantities take the form of electrical or magnetic/ electromagnetic signals capable of being stored, transferred, combined, compared, and otherwise manipulated. It is convenient at times, principally for reasons of common usage, to refer to these signals as bits, values, parameters, items, elements, objects, symbols, characters, terms, numbers, or the like. It should be noted, however, that all of these terms and similar terms are to be associated with the appropriate physical quantities and are merely convenient labels applied to these quantities.

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EP19789212.8A EP3781241B1 (en) 2018-04-17 2019-04-12 Liquid ventilator to induce tidal liquid ventilation and/or hyporthermia
KR1020207032986A KR102774314B1 (ko) 2018-04-17 2019-04-12 일회 액체 환기 및/또는 저체온을 유발하는 액체 환기장치 및 방법
CA3097435A CA3097435A1 (en) 2018-04-17 2019-04-12 Liquid ventilator and method to induce tidal liquid ventilation and/or hyporthermia
CN201980040240.5A CN112770800B (zh) 2018-04-17 2019-04-12 液体呼吸机和诱发潮气液体通气和/或低体温症的方法
JP2021506017A JP7386843B2 (ja) 2018-04-17 2019-04-12 一回液体換気および／または低体温を誘導するための液体換気装置および方法
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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN110987077A (zh) * 2019-12-18 2020-04-10 脉象医疗科技(苏州)有限公司 一种制氧机自动测试系统及方法
CN111324154A (zh) * 2020-01-20 2020-06-23 深圳市科曼医疗设备有限公司 混合腔压力控制方法、呼吸机设备和计算机可读存储介质
RU218907U1 (ru) * 2023-04-20 2023-06-16 Федеральное государственное автономное образовательное учреждение высшего образования "Севастопольский государственный университет" Аппарат жидкостного дыхания замкнутого типа в условиях изменяющегося гипербарического давления окружающей среды
EP4142841A4 (en) * 2020-04-29 2024-05-22 LifeAir Medical Corporation VENTILATION SYSTEM WITH REMOVABLE AIRWAYS

Families Citing this family (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US12257385B2 (en) * 2021-09-29 2025-03-25 Alcor Life Extension Foundation, Inc. Liquid ventilation system
CN114028208B (zh) * 2021-11-26 2025-02-14 查显进 亚低温氧疗仪
EP4647097A1 (en) * 2024-05-07 2025-11-12 Orixha Liquid ventilation connector

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CA2451261A1 (en) * 2002-11-29 2004-05-29 Universite De Sherbrooke Method and apparatus for conducting total liquid ventilation with control of residual volume and ventilation cycle profile
WO2012062266A1 (de) * 2010-10-11 2012-05-18 Technische Universität Dresden Vorrichtung und verfahren zur beatmung
US20120226337A1 (en) * 2011-03-03 2012-09-06 Inserm (Institut National De La Sante Et De La Recherche Medicale) Method and System for Treatment of a Body of a Mammal in Cardiac Arrest
US20160271348A1 (en) * 2013-06-25 2016-09-22 Socpra Sciences Et Génie S.E.C. Indirect measurement in a total liquid ventilation system

Family Cites Families (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5437272A (en) * 1991-05-01 1995-08-01 Alliance Pharmaceutical Corp. Perfluorocarbon associated gas exchange
US5335650A (en) * 1992-10-13 1994-08-09 Temple University - Of The Commonwealth System Of Higher Education Process control for liquid ventilation and related procedures
AU2002362045A1 (en) * 2001-12-04 2003-06-17 Minnesota High-Tech Resources, Llc Breathable gas mixtures to change body temperature
US7909031B2 (en) * 2005-06-09 2011-03-22 Temple Univesity - Of The Commonwealth System of Higher Education Process for transient and steady state delivery of biological agents to the lung via breathable liquids
CA2623756A1 (en) * 2005-09-20 2007-03-29 Lutz Freitag Systems, methods and apparatus for respiratory support of a patient
US7810497B2 (en) * 2006-03-20 2010-10-12 Ric Investments, Llc Ventilatory control system
CN102451506B (zh) * 2010-10-19 2015-04-08 袁含光 一种呼吸机气流控制装置
CN103585707A (zh) * 2013-11-25 2014-02-19 姜力骏 一种完全液体通气呼吸机

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CA2451261A1 (en) * 2002-11-29 2004-05-29 Universite De Sherbrooke Method and apparatus for conducting total liquid ventilation with control of residual volume and ventilation cycle profile
WO2012062266A1 (de) * 2010-10-11 2012-05-18 Technische Universität Dresden Vorrichtung und verfahren zur beatmung
US20120226337A1 (en) * 2011-03-03 2012-09-06 Inserm (Institut National De La Sante Et De La Recherche Medicale) Method and System for Treatment of a Body of a Mammal in Cardiac Arrest
US20160271348A1 (en) * 2013-06-25 2016-09-22 Socpra Sciences Et Génie S.E.C. Indirect measurement in a total liquid ventilation system

Non-Patent Citations (6)

* Cited by examiner, † Cited by third party
Title
MICHEAU ET AL.: "A Liquid Ventilator Prototype for Total Liquid Ventilation Preclinicla Studies", PROGRESS IN MOLECULAR AND ENVIRONMENTAL BIOENGINIEERING - FROM ANALYSIS AND MODELING TO TECHNOLOGY APPLICATIONS, 1 August 2011 (2011-08-01)
NADEAU ET AL.: "Core Body Temperature Control by Total Liquid Ventilation Using a Virtual Lung Temperature Sensor", IEEE TRANSACTIONS ON BIOMEDICAL ENGINEERING, vol. 61, no. 12, December 2014 (2014-12-01), pages 2859 - 2868, XP055370950, DOI: 10.1109/TBME.2014.2332293 *
NADEAU ET AL.: "Patient-specific optimal cooling power commandfor hypothermia induction by liquid ventilation", CONTROL ENGINEERING PRACTICE, vol. 77, June 2018 (2018-06-01), pages 109 - 117, XP055644627 *
ROBERT ET AL.: "A Regulator for Pressure-Controlled Total-Liquid Ventilation", IEEE TRANSACTIONS ON BIOMEDICAL ENGINEERING, vol. 57, no. 9, September 2010 (2010-09-01), pages 2267 - 2276, XP011343326, DOI: 10.1109/TBME.2009.2031096
ROBERT ET AL.: "A supervisor for volume-controlled tidal liquid ventilator using independent piston pumps", BIOMEDICAL SIGNAL PROCESSING AND CONTROL, vol. 2, no. 3, September 2007 (2007-09-01), pages 267 - 274, XP022303108, DOI: 10.1016/j.bspc.2007.07.010
See also references of EP3781241A4

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN110987077A (zh) * 2019-12-18 2020-04-10 脉象医疗科技(苏州)有限公司 一种制氧机自动测试系统及方法
CN110987077B (zh) * 2019-12-18 2022-03-11 脉象医疗科技(苏州)有限公司 一种制氧机自动测试系统及方法
CN111324154A (zh) * 2020-01-20 2020-06-23 深圳市科曼医疗设备有限公司 混合腔压力控制方法、呼吸机设备和计算机可读存储介质
EP4142841A4 (en) * 2020-04-29 2024-05-22 LifeAir Medical Corporation VENTILATION SYSTEM WITH REMOVABLE AIRWAYS
RU218907U1 (ru) * 2023-04-20 2023-06-16 Федеральное государственное автономное образовательное учреждение высшего образования "Севастопольский государственный университет" Аппарат жидкостного дыхания замкнутого типа в условиях изменяющегося гипербарического давления окружающей среды

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