US20100004571A1 - Driving control of a reciprocating cpr apparatus - Google Patents

Driving control of a reciprocating cpr apparatus Download PDF

Info

Publication number
US20100004571A1
US20100004571A1 US12/523,082 US52308208A US2010004571A1 US 20100004571 A1 US20100004571 A1 US 20100004571A1 US 52308208 A US52308208 A US 52308208A US 2010004571 A1 US2010004571 A1 US 2010004571A1
Authority
US
United States
Prior art keywords
gas
compression
piston
reciprocating
valve
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.)
Abandoned
Application number
US12/523,082
Other languages
English (en)
Inventor
Anders Nilsson
Peter Sebelius
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.)
Physio Control Inc
Original Assignee
Jolife AB
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 Jolife AB filed Critical Jolife AB
Assigned to JOLIFE AB reassignment JOLIFE AB ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: NILSSON, ANDERS, SEBELIUS, PETER
Publication of US20100004571A1 publication Critical patent/US20100004571A1/en
Assigned to PHYSIO-CONTROL, INC. reassignment PHYSIO-CONTROL, INC. STATEMENT OF ASSIGNMENT Assignors: JOLIFE AB
Abandoned legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H31/00—Artificial respiration or heart stimulation, e.g. heart massage
    • A61H31/004—Heart stimulation
    • A61H31/006—Power driven
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2201/00—Characteristics of apparatus not provided for in the preceding codes
    • A61H2201/12—Driving means
    • A61H2201/1238—Driving means with hydraulic or pneumatic drive
    • A61H2201/1246—Driving means with hydraulic or pneumatic drive by piston-cylinder systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2201/00—Characteristics of apparatus not provided for in the preceding codes
    • A61H2201/16—Physical interface with patient
    • A61H2201/1657—Movement of interface, i.e. force application means
    • A61H2201/1664—Movement of interface, i.e. force application means linear
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2201/00—Characteristics of apparatus not provided for in the preceding codes
    • A61H2201/50—Control means thereof
    • A61H2201/5007—Control means thereof computer controlled
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2201/00—Characteristics of apparatus not provided for in the preceding codes
    • A61H2201/50—Control means thereof
    • A61H2201/5058—Sensors or detectors
    • A61H2201/5064—Position sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2201/00—Characteristics of apparatus not provided for in the preceding codes
    • A61H2201/50—Control means thereof
    • A61H2201/5058—Sensors or detectors
    • A61H2201/5064—Position sensors
    • A61H2201/5066—Limit switches
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H2201/00—Characteristics of apparatus not provided for in the preceding codes
    • A61H2201/50—Control means thereof
    • A61H2201/5058—Sensors or detectors
    • A61H2201/5092—Optical sensor
    • A—HUMAN NECESSITIES
    • 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. mouth-to-mouth respiration; Tracheal tubes

Definitions

  • the present invention relates to a method of sensing the chest compression depth in a reciprocating apparatus for cardio-pulmonary resuscitation (CPR) driven by a compressed gas, a method of controlling the amount of compressed gas used for driving a reciprocating apparatus for cardiopulmonary resuscitation (CPR), and a correspondingly operated reciprocating CPR apparatus.
  • CPR cardio-pulmonary resuscitation
  • CPR cardio-pulmonary resuscitation
  • repeated compressions are administered by hand or by apparatus to the chest of the person being resuscitated to maintain circulation and oxygenation of blood. Concomitant with the compressions electrical shocks are provided to the patient to make the heart beat again.
  • Gas-driven reciprocating CPR apparatus have been known in the art and used in practice for a long time; see, for instance, U.S. Pat. Nos. 3,209,747 (Guentner) and 3,277,887 (Thomas). Providing compressions of correct depth is an important factor for success of the method.
  • Compression Depth signifies the maximum sternal deflection during a compression/decompression cycle.
  • An appropriate Compression Depth for adult persons corresponds to a sternal deflection of 20%; the compression depth for a chest with an anterior-posterior diameter of 25 cm thus is 5 cm.
  • compression depth in the following refers to a sternal deflection during a compression/decompression cycle smaller than the maximum deflection or to sternal deflection in general.
  • Shallow compressions may be insufficient to restore circulation and oxygenation while compressions that are too deep may damage the ribs and the soft tissues of the chest. There is thus an optimal Compression Depth or a narrow range of optimal Compression Depths.
  • Administration of compressions of optimal Compression Depth may be controlled by administering compressions of a given force.
  • a desired Compression Depth may be set by an operator; it may be optionally changed during resuscitation.
  • the Compression Depth in a CPR apparatus can be set by limiting the stroke of the piston in the apparatus to the average optimal Compression Depth for an adult person.
  • a given compression force results in a compression to a Compression Depth at which the compression force is balanced by the resistive force of the chest tissues.
  • a problem with CPR apparatus driven by a compressed gas is limited gas supply, since the apparatus may be used for an hour or more to provide compressions to the patient during transport to a hospital by, for instance, an ambulance.
  • Still another object of the invention to provide a method of optimizing the use of compressed breathing gas for driving the apparatus based on the determination of the Compression Depth and/or a compression depth.
  • An additional object of the invention is to provide a reciprocating apparatus for cardio-pulmonary resuscitation driven by a compressed gas, provided with said means and control means for optimizing the use of driving gas.
  • a method of sensing the Compression Depth and/or a compression depth in a reciprocating apparatus for cardio-pulmonary resuscitation (CPR) driven by a compressed gas and comprising a reciprocating part and a non-reciprocating part the method comprising arranging a sensor mounted on the non-reciprocating part capable of sensing a signal emanating from the reciprocating part at a selected position thereof; transmitting the signal to a microprocessor unit that records its arrival time.
  • CPR cardio-pulmonary resuscitation
  • non-reciprocating part comprises a cylindrical housing having a top wall, a bottom wall and a side wall
  • reciprocating part to comprise a piston disposed in the housing so as to allow displacement thereof by a compressed gas adduced to an upper compartment in the housing defined by the top wall, a portion of the side wall, and the piston.
  • displacement in the opposite direction may be effected by adducing a compressed gas to a lower compartment in the housing defined by the bottom wall, a portion of the side wall, and the piston.
  • indications of direction and position such as “upper”, “upwards”, “top” and “lower”, “bottom”, “downwards”, are governed by this disposition of the CPR apparatus in respect of the patient.
  • the cylinder walls and the piston are preferably of a diamagnetic material, in particular an organic polymer material, for instance polystyrene or polyester, in particular polyamide, possibly reinforced with organic or inorganic fibre.
  • a diamagnetic material in particular an organic polymer material, for instance polystyrene or polyester, in particular polyamide, possibly reinforced with organic or inorganic fibre.
  • contactless sensing is preferred, sensing by contact is comprised by the method of the invention.
  • contactless sensing it is preferred to sweep one or several magnetic or radiation sensors mounted at the non-reciprocating part with a magnetic field or radiation, respectively, emanating from a corresponding field or radiation source mounted at or deflected or reflected by the reciprocating part, thereby giving rise to an electric signal in a swept sensor.
  • the radiation source is one emitting radiation in the UV, visible or IR range of the spectrum.
  • the radiation source is an ultrasound source
  • the radiation detector is an ultrasound detector.
  • the one or several magnetic sensors are disposed on the outer face of the side wall, in particular in a line or array extending in an axial direction.
  • an axial direction is one extending in parallel with the axis of the cylindrical housing.
  • the magnetic field source is a permanent ring or rod magnet mounted on or in the piston.
  • the piston should be of a diamagnetic material, such as glass or carbon fibre reinforced polyamide.
  • Particularly suited materials for the ring or rod magnet are Al—Ni, neodymium and samarium cobalt.
  • Preferred magnetic sensors comprise Hall-effect elements such as unipolar, bipolar, and omnipolar Hall-effect digital switches.
  • the radiation source is disposed at the inner face of the bottom, its radiation being directed at the bottom face of the piston, which is diffusely or mirroring reflective or comprises a diffusely or mirroring reflective material capable of reflecting or mirroring, respectively, of more than 20%, preferably more than 50%, even more preferred more than 80% or the incident radiation.
  • the one or several radiation sensors are disposed at the inner face of the bottom. If there are two or more radiation sensors they are preferably disposed in a line or an array, such as a line or array extending in a radial direction. In this application “radial direction” is a direction extending radially from the centre of the piston.
  • the detection of the position of the piston may be based on total reflected radiation detected by the one or several radiation sensors or by detection of reflected radiation by two or more radiation sensors so disposed that each sensor receives a maximum of reflected radiation from a position of the piston that is different from that from which an adjacent sensor receives a maximum of reflected radiation.
  • the radiation source is a source of visible, UV or IR light.
  • a preferred source of radiation is a light-emitting diode (LED).
  • Preferred optical sensors are sensors capable of detecting the radiation emitted from the radiation source, in particular sensors capable of detecting radiation reflected by the reflective material, such as photodiodes and phototransistors.
  • the contactless method of the invention and the corresponding means thus allow to monitor the position of the compression pad over time, such as over one or several compression cycles.
  • an reciprocating CPR apparatus with a pre-set compression depth by use of a physical Compression Depth limiter it is possible to monitor the moment at which, or whether, the Compression Depth is reached by an electrical contact mounted at or in proximity of the limiter, which is actuated by the piston so as to close or open an electrical circuit, thereby producing an electrical recordable signal.
  • monitoring the Compression Depth and/or a compression depth can be used to optimize, that is, to minimize the consumption of driving gas in a reciprocating CPR apparatus of the aforementioned kind. This allows to substantially reduce the consumption of driving gas by CPR apparatus.
  • the initial resistance of the chest of adult persons to a compression of 50 mm is in the order of about 300 N to 400 N.
  • a gas-driven reciprocating CPR apparatus has to be driven with a pressure that is substantially higher than the pressure required to just overcome this resistance.
  • This pressure is, of course, also dependent on the area of the piston in the CPR apparatus.
  • a suitable driving gas pressure is from about 2.5 to 4 bar, preferably about 3 bar.
  • a suitable piston area for a driving gas pressure of 3 bar is about 20 cm 2 .
  • This driving gas pressure is however only needed during a short period from the start of providing chest compressions to the patient, such as for a period of one or two minutes. During this period the resistance of the chest decreases by about 50 percent. In consequence, a lower pressure is required to administer compressions of same depth during the following steady-stated period in which the resistance of the chest does not change.
  • the provision of driving gas to the CPR apparatus is only required during a portion of the compression phase, in particular over a period extending from the onset of the compression phase to shortly before the compression depth is reached, such as from 10 to 50 milliseconds, more preferred from 20 to 40 milliseconds, most preferred about 30 milliseconds before the Compression Depth is reached.
  • the consumption of driving gas can be substantially reduced, such as by 40 percent and even up to 50 percent.
  • the onset of the compression phase is determined by the opening of the valve controlling the supply of gas to the cylinder. The cylinder starts its downward movement shortly thereafter.
  • the end of the compression phase and the start of the decompression phase is determined by the opening of a valve for venting the used driving gas from the upper compartment.
  • the piston can be returned to its starting position by adducing compressed driving gas to the lower compartment.
  • the compression pad which abuts the breast of the patient and carries a circumferential soft sealing rim or is provided with an adhesive, brings the patient's breast back to its original position. In the absence of such breast returning means the passive return by the chest's resilience is much slower and not its original position.
  • a method of controlling the amount of compressed gas, such as compressed air, used for driving a CPR apparatus of the aforementioned kind over a reciprocating cycle comprising a method of determining the compression Depth and/or a compression depth, including determining the moment at which the Compression Depth and/or a compression depth is reached; that moment is preferably determined by sensor means mounted at a non-reciprocating part of the apparatus sensing radiation reflected from a reciprocating part of the apparatus or a magnetic field moving with a reciprocating part of the apparatus.
  • the method of controlling the amount of compressed gas used for driving a CPR apparatus is based on the insight that the supply of compressed gas to the compartment of the cylinder in which the gas expands and drives the piston against the resistance of the patient's chest tissues is a dynamic process.
  • equilibrium between the gas pressure in the reservoir, in which partially decompressed gas from the gas cylinder is stored at an about constant pressure, and said compartment is not established.
  • the pressure of the gas fed to the compartment must be substantially higher than the pressure that is needed to displace the piston to the Compression Depth in a situation of equilibrium.
  • the amount of gas used required for compression to the Compression Depth can be substantially reduced by stopping the supply of gas to the compartment at the moment when the compression depth is reached or, preferably, shortly before that moment.
  • the moment at which the Compression Depth and/or a compression depth is reached is used for positional control of valve means through which the compressed gas is adduced to the upper compartment in the housing.
  • the microprocessor means operates the valve means, for instance a solenoid valve control unit comprising one or several solenoid valves, so as to stop the flow of compressed gas to the upper compartment of the housing.
  • the prior point in time is from 0 to 50 milliseconds prior, in particular from 0 to 30 milliseconds prior, most preferred about 10 to 15 milliseconds prior to the moment at which the compression depth is reached.
  • the valve means to stop providing driving gas to the upper compartment after at point in time when the pressure of the gas in the upper compartment is from 30 to 70 percent of the pressure of the driving gas, more preferred from 40 to 60 percent, most preferred about 50 percent.
  • a preferred driving gas pressure is from 2.5 to 4 bar, more preferred about 3 bar. It is also preferred for the portion of the compression phase during which the valve means allow driving gas to enter the upper compartment to extend from the start of the compression phase until a point in time when from 25 percent to 40 percent of the length of the compression phase has passed.
  • the method of controlling the amount of compressed gas used for driving a reciprocating apparatus for cardiopulmonary resuscitation (CPR) comprising a valve means for controlling the provision of driving gas to a reciprocating part of the apparatus and for venting of the used driving gas from the apparatus, comprises: (a) operating the valve means at the start of a compression/decompression cycle to provide driving gas; (b) operating the valve means during the compression phase to stop provision of driving gas;
  • Step (c) operating the valve means at the end of the compression phase to vent the driving gas from the apparatus.
  • Step (b) is preferably initiated at a point in time when the pressure of the provided driving gas is from 30 percent to 70 percent of the pressure of the driving gas, more preferred from 40 percent to 60 percent of the pressure of the driving gas, most preferred about 50 percent. It is also preferred for step (b) to be initiated at a point in time which is at from 25 percent to 40 percent of the length of the compression phase, in particular at a point in time before the moment at which a compression pad of the reciprocating part has reached the Compression Depth.
  • Mechanical control of the Compression Depth is obtained by mechanically stopping the piston at a desired length of stroke by, for instance, the bottom of the cylinder or a circumferential flange arranged on the inner face of the cylinder between the piston and the bottom.
  • the method of control comprises determining the moment at which the Compression Depth is reached during a reciprocating cycle, which moment may have been determined in (a) preceding reciprocating cycle(s).
  • the method of control comprises determining the moment at which a compression depth is reached during a reciprocating cycle, which moment may have been determined in (a) preceding reciprocating cycle(s).
  • the means for determining the moment at which the Compression Depth and/or a compression depth is reached include those described above but can also, for instance, comprise a simple mechanically operated electric switch that is switched by impact of, for instance, the piston at the moment or close to the moment at which the piston is stopped by the stopping means.
  • the method is used for positional control of valve means through which the compressed gas passes into the upper compartment in the housing.
  • the microprocessor means operates the valve means, for instance a solenoid valve control unit comprising one or several solenoid valves, so as to stop the flow of compressed gas to the upper compartment of the housing.
  • valve means for instance a solenoid valve control unit comprising one or several solenoid valves, so as to stop the flow of compressed gas to the upper compartment of the housing.
  • “Slightly prior to that moment” signifies from 0 to 50 milliseconds, in particular from 0 to 30 milliseconds, most preferred about 10 to 15 milliseconds prior to the moment at which the piston reaches the compression depth.
  • the stroke length of the CPR apparatus in which the compression depth is mechanically controlled may be fixed or can be set prior to or even during CPR.
  • a CPR apparatus comprising a housing and a reciprocating piston mounted in the housing driven by a pressurized gas, in particular a pressurized breathing gas such as air.
  • the apparatus further comprises a means for sensing the compression depth, in particular a means for contactless sensing.
  • a compression pad is mounted to the piston via a plunger and is placed on the chest of a patient above the sternum. The reciprocating movement of the piston is so transferred to the pad, and it is by the pad that the patient's chest is compressed to the Compression Depth.
  • the frequency of compression can be varied but is typically in the order of 60 to 120 cycles per minute.
  • the sensing means comprises a source of radiation or of a magnetic field and one or several radiation or magnetic field sensors, respectively. It is preferred for the source of radiation and for the optical sensor(s) to be mounted at a non-reciprocating part of the apparatus and for the sensing means to comprise a reflective area disposed on a top or bottom face of the piston. It is preferred for the source of magnetic field to be mounted at a reciprocating part of the apparatus, in particular the piston, and for the field detection source to be mounted at a non-reciprocating part of the apparatus, in particular an inner face of the bottom wall or the top wall.
  • the radiation or magnetic sensor(s) are electrically connected to a microprocessor unit capable of comparing the sensor signal with a given signal and to store sensor signal data over one or more cycles.
  • the CPR apparatus comprises a valve means, in particular a solenoid valve means, controlled by means of compression depth and time data stored in the microprocessor memory related to the time at which the piston reached the Compression Depth during a reciprocating cycle, in particular an earlier reciprocating cycle.
  • control of driving gas according to the method of the invention does not comprise the optional provision of driving gas to embodiments of the CPR apparatus of the invention at the end of the compression phase to push the piston back to its starting position.
  • FIG. 1 is a sectional view of a first embodiment of the apparatus of the invention disposed on the chest of a patient shown in a transverse section at the level of the eight thoracic vertebra (T8) and viewed in a cranial direction;
  • FIG. 1 a is a detail view of the embodiment of FIG. 1 , in the same view and enlarged;
  • FIG. 1 b is a section A-A ( FIG. 1 ) through a modification of the apparatus of FIG. 1 ;
  • FIG. 1 c is a detail view of another modification of the apparatus of FIG. 1 showing solenoid valve control unit with a pair of solenoid valves;
  • FIGS. 2 a - 2 h show the embodiment of FIG. 1 and in the same view, in consecutive states of chest compression by reciprocating displacement of its piston and compressing pad;
  • FIG. 3 is a block scheme of a solenoid valve control program
  • FIGS. 4 a - 4 d show another embodiment of the apparatus of the invention, in the same view as in FIG. 1 and, in FIGS. 4 c and 4 d , partially enlarged;
  • FIG. 5 shows a further embodiment of the apparatus of the invention, in the same view as in FIG. 1 ;
  • FIGS. 6 a - 6 c are graphs illustrating the effect of driving gas valve opening times on gas consumption in reaching and maintaining a desired compression depth against a given resilient force in CPR model experiments;
  • FIG. 7 is a rough sketch of the compression testing apparatus used in the experiments illustrated in FIGS. 6 a - 6 c.
  • the embodiment of the apparatus 1 of the invention shown in FIGS. 1-2 h comprises a cylinder housing of a diamagnetic material having a side wall 2 , a bottom 3 and a top wall 4 .
  • a piston 5 with a circumferential sealing 9 is mounted in the housing and defines an upper compartment A and a lower compartment B.
  • a plunger 6 extends downwards from the centre of the piston 5 , passing through a central bore in the bottom 3 of the housing. At its free end the plunger 6 carries a chest compression pad 7 provided with a flexible circumferential lip 8 .
  • the piston 5 /plunger 6 /compression pad 7 is mounted displaceably in the cylinder housing.
  • a neodymium magnet ring 14 is mounted at the lower face of the piston 5 with its south pole S facing the side wall 2 .
  • An array of unipolar Hall-Effect digital switches (“unipolar Hall switches”) 15 , 16 , 17 , 18 , 19 is mounted at the outer wall of the cylinder 1 in an axial direction.
  • the unipolar Hall switches 15 , 16 , 17 , 18 , 19 are characterized by their magnetic operating threshold. If the Hall cell of a switch 15 , 16 , 17 , 18 , 19 is exposed to the magnetic field of the south pole exceeding the operating threshold, the output transistor is switched on. If the field drops below the switching threshold, the transistor is switched off.
  • each of the unipolar Hall switches 15 , 16 , 17 , 18 , 19 is grounded at 23 whereas the other is fed with 3 V DC by lines 15 ′, 16 ′, 17 ′, 18 ′, 19 ′, respectively, connected to a microprocessor unit 13 .
  • FIG. 1 a the field lines 24 of the magnet's 14 south pole S are shown in respect of unipolar Hall switches 18 , 19 to illustrate how the latter are influenced during a displacement of the plunger 6 .
  • the effect (Hall effect) by which the switches 15 , 16 , 17 , 18 , 19 are closed by the influence of the field of the magnet 14 allows to monitor the passage of the plunger by the microprocessor unit 13 ( FIG. 3 ).
  • the circuit of the respective switch 15 , 16 , 17 , 18 or 19 is closed, the current passing a closed switch being recorded by the microprocessor unit 13 .
  • the respective switch is again opened except for if the plunger stops in a position in which the magnetic field does cover it after stop. This allows the microprocessor unit 13 to keep track of the movement of the piston 5 /plunger 6 /pad 7 assembly and, in particular, its position at the end of its downward or, less important, upward movement, and to control the provision of compressed breathing gas to compartment A by the solenoid valve based on that position.
  • unipolar Hall switches in the embodiment of FIGS. 1 to 2 h is confined to five.
  • An embodiment that allows to obtain fine tuning of positional control can comprise a higher number of unipolar Hall switches and/or have the switches disposed in the region of the compression depth level where the determination of position of piston 5 /plunger 6 /compression pad 7 is most important.
  • Other Hall-effect switches like bipolar and omnipolar Hall-effect switches may be used for sending the field of magnet 14 .
  • the ring magnet 14 is exchanged for a rod magnet 6 ′ ( FIG. 1 b ).
  • a counter weight 27 is mounted diametrically opposite to the magnet 6 ′ at the lower face of the piston 5 ′.
  • the use of a rod magnet 6 ′ requires the arrangement of a means preventing rotation of the piston 5 ′.
  • the rotation preventing means comprises two diametrically opposite axially extending flanges 28 protruding from inner face of the cylinder side wall 2 ′ and co-operating with diametrically opposite axially extending slits in the side wall of piston 5 ′.
  • a Hall-effect switch 18 ′ mounted at the outer face of the side wall 3 ′ opposite to the south pole of magnet 14 ′.
  • the upper compartment A of the housing is defined by the top face of the piston 5 , a first portion of the side wall 2 of the housing, and the top wall 4 of the housing, whereas its lower compartment B is defined by the bottom face of the piston 5 , the bottom face of the magnet 14 , a second portion of the side wall 2 and the bottom wall 3 .
  • An opening 22 in the bottom wall 3 allows air to enter into compartment B or to be expelled from it depending on the direction of displacement of the piston 5 .
  • a tube 10 for providing compressed breathing gas from a gas supply such as a gas cylinder or other container of compressed breathing gas (not shown) is mounted at and communicates with an opening 25 in the top wall 4 . Near the opening 25 a venting tube 21 branches off from tube 10 . Tube 21 can be put in communication with a breathing mask (not shown) borne by the patient under cardiopulmonary resuscitation.
  • a three-way solenoid valve 11 controlled by a solenoid control unit 12 is mounted in the lumen of tube 10 at the branching of the venting tube 21 . In a first position P 1 the solenoid valve 11 allows compressed breathing gas to enter compartment A through opening 25 . In a second position P 2 the solenoid valve 11 allows to vent compressed air in compartment A through venting tube 22 .
  • the solenoid valve 11 is only shown schematically in the Figures; its design allows switching between positions P 1 and P 2 without passing an intermediate position in which the lumina of tubes 10 and 21 and the compartment A are in simultaneous communication.
  • the solenoid valve is actuated by a solenoid valve control unit 12 receiving actuation signals from the microprocessor unit 13 via line 20 .
  • the microprocessor unit 13 and the solenoid valve control unit 12 are energized by a dry battery (not shown).
  • the three-way solenoid valve 11 of the embodiment of FIGS. 1 and 2 a to 2 h can be exchanged for a pair of solenoid valves 11 ′, 11 ′′ actuated by a solenoid valve control unit 12 ′ ( FIG. 1 c ).
  • Reference numbers 4 ′, 10 ′, 21 ′ and 25 ′ identify elements corresponding to elements 4 , 10 , 21 and 25 , respectively, of the embodiment of FIGS. 1 to 2 h.
  • the compressed breathing gas is decompressed in controlled manner (not shown) to a working pressure, which is kept about constant during CPR.
  • the gas of working pressure is suitable held in a reservoir from which the gas of working pressure is adduced to the compartment A via tube 10 so as to provide it at an about constant gas pressure over time. This allows the provision of a controlled compression force via the piston 5 , the plunger 6 , and the pad 7 to the chest of a patient.
  • the gas pressure in the compartment 10 (the pressure of the “provided” driving gas) is not in equilibrium with the pressure of the driving gas at the source over an initial portion of the compression phase.
  • the compression pad 7 is loosely placed on the chest 30 of a person to be provided chest compressions ( FIG. 1 ).
  • the person is in a recumbent position with the pad 7 placed on the skin 31 above the sternum 32 .
  • Reference numbers denote: 33 , right ventricle; 34 , left ventricle; 35 , esophagus; 36 , descending aorta; 37 , body of the eight thoracic vertebra (T8); 38 , spinal cord; 39 left arc of ribs.
  • FIG. 2 a The position at the start of dispensation of chest compression is shown in FIG. 2 a , which corresponds to FIG. 1 except for that only the skin 31 of the patient's chest in the sternal region is shown.
  • the uncompressed level of the skin 31 at the application site of the pad 7 is designated O.
  • the solenoid valve 11 is in the venting position P 1 and the plunger is in an unloaded state.
  • By opening of the venting valve 11 (valve position P 2 ) compressed air is made to flow from the gas cylinder to tube 10 and to enter compartment A through opening 25 .
  • the increasing air pressure in compartment A starts to force the piston 5 downwards in the direction of bottom wall 3 ( FIG. 2 b ; start of downward movement of piston 5 indicated by an arrow).
  • the south pole S of the magnet 14 is disposed between Hall switches 15 and 16 .
  • the microprocessor unit 13 keeps track of the position of the piston 5 during its downward (and upward, if desired) movement, and recognizes the exact moment at which the piston 5 /plunger 6 /rod 7 assembly has reached its extreme position during its downward movement ( FIG. 2 d , indicating the infinitesimal last downward movement of piston 5 /plunger 6 /rod 7 assembly prior to stop with the valve 11 in position P 1 ; FIG. 2 e , the moment of stop with the valve 11 in position P 1 ; and, at the same moment, FIG. 2 f , an immediate switch of the valve 13 from position P 1 to P 2 .
  • the switch of the solenoid valve 11 from P 1 to P 2 can be made to occur slightly earlier, that is, prior to the piston 5 /plunger 6 /rod 7 assembly reaching its downward stop position by programming of the microprocessor 13 correspondingly.
  • the recognition of the time when the piston 5 /plunger 6 /rod 7 assembly reaches its lower end or bottom position moment thus is used for control of the solenoid valve so as to switch it from position P 2 to P 1 .
  • the flow of compressed gas into compartment A is stopped at the moment where the piston 5 /plunger 6 /rod 7 assembly reaches the desired extreme position (Compression Depth) or slightly before that moment. Thereby the provision of driving gas is optimized and thus economized.
  • compartment A is vented via tube 21 .
  • the driving gas is a breathing gas
  • the vented gas or a portion thereof which is still of a slightly higher pressure than ambient air, can be adduced to the patient's lungs via a breathing mask or by intubation (not shown).
  • the venting of compartment A stops the load on the piston 5 /plunger 6 /rod 7 assembly ( FIG. 2 g ) and thus the compression of the patient's chest.
  • the resilient nature of the chest makes it expand and push the piston 5 /plunger 6 /rod 7 assembly back to its start position ( FIG. 2 h ).
  • the microprocessor unit 13 of the apparatus of the invention is programmed in a manner so as to sample and store positional data over one or several cycles, and to use such data for control of a later cycle.
  • FIGS. 1 to 2 h has been simplified in respect to commercially available apparatus of this kind in regard of ancillary features.
  • the upward movement of the piston 5 /plunger 6 /rod 7 assembly of this embodiment of the apparatus of the invention is passive, that is, driven by the resilient force of the patient's chest, whereas it can be advantageously be driven by means of the compressed breathing gas used in the apparatus.
  • a substantially more complex arrangement of valves and gas lines for adducing compressed gas to compartment B and venting it from there is required.
  • the position of the piston 105 and thus the compression depth is determined by means of a source of visible light 114 and a number of photo detectors 143 , 144 , 145 , 146 , 147 , 148 , 149 , all disposed in a radial direction, with the light source 114 innermost, on the inner face of bottom wall 103 .
  • the light source 114 is a red light photodiode whereas the photo detectors 113 - 119 are silicon based photodiodes operated in photoconductive mode.
  • the narrow and substantially parallel beam of light 124 ′ of the photodiode 114 is directed at the lower face of the piston 114 , which is provided with a ring mirror 130 , at an angle ⁇ and in the same a radial direction in respect of the piston 105 axis as that of the disposition of photo detectors 113 - 119 .
  • the incident beam 124 ′ is reflected at the same angle ⁇ in the direction of photo detectors 113 - 119 disposed on the bottom 103 .
  • the distance between the inner face of the bottom 103 and the lower face of the piston 105 provided with the mirror element 130 determines which of the photo detectors 143 - 149 is hit by the reflected beam 124 ′′.
  • the reflected beam 124 ′′ hits the next but innermost photo detector 148 , whereas in a position of the piston near the top wall 104 (distance d 2 , FIG. 4 d ) the next but outermost photo detector 144 is hit.
  • the reflected beam 124 ′′ thus will sweep, depending on its start position and its end position (Compression Depth position) over all or only some of the photo detectors in a radially inward direction.
  • the photo diode 114 and the photo detectors 143 , 144 , 145 , 146 , 147 , 148 , 149 are connected to a microprocessor unit 113 via separate conductors 114 ′, 143 ′, 144 ′, 145 ′, 146 ′, 147 ′, 148 ′, 149 ′, respectively, which are bundled in a cable 131 .
  • the microprocessor 113 uses the signals from the photo detectors 143 - 149 in a time frame to control gas flow in the apparatus 100 by a solenoid valve 111 operated by a solenoid control unit 112 in a manner corresponding to that described in Example 1 for the electric signals generated by the Hall-effect switches 15 , 16 , 17 , 18 , 19 .
  • a solenoid valve 111 operated by a solenoid control unit 112 in a manner corresponding to that described in Example 1 for the electric signals generated by the Hall-effect switches 15 , 16 , 17 , 18 , 19 .
  • 4 a - 4 d reference numbers 106 , 110 , 120 , 121 refer to a plunger 106 carrying a chest compression pad (not shown), a tube 110 for adducing compressed breathing gas, to a electrical connection 120 between the microprocessor unit 112 and the solenoid control unit 112 , and to a tube 121 for venting compressed breathing gas used for displacement of the piston 105 , respectively.
  • the stroke of the piston 305 is limited by an annular stop 320 .
  • the piston 305 hits and thereby closes a contact switch 315 of an electrical circuit comprised by a microprocessor unit 313 .
  • the microprocessor unit 313 thereby receives information about the moment at which the Compression Depth is reached. Based on this information the microprocessor's 313 issues a closing command to the control unit 312 of solenoid valve 311 , in particular in a following cycle prior to the expected time of contact.
  • a gas inlet tube 340 to provide driving gas to the closed lower chamber B of the cylinder housing 302 , 303 , 304 illustrates the principle of assisted piston 305 return that can be applied to all embodiments of the invention, if desired.
  • t_open which controls the time the air supply port for the compression phase is open
  • t_open 300 ms, which is the maximum possible value.
  • the apparatus then performs one cycle (compression and decompression) with this setting.
  • the signal from the Hall effect element is sampled. If the piston reaches the bottom of the cylinder it will be registered by the Hall effect sensor signal as a high voltage, sampled by the function “read digital input signal_of_hall_effect_element” and then written to the variable is_down.
  • is_down is the variable that indicates whether the piston has reached its bottom position during the cycle, and then determines which adjustment of t_open shall be performed.
  • variable t_open is lowered by 20 ms. This is repeated for every cycle until there is no trigger detected. During this last cycle the piston is likely to have stopped just before it reached the Hall effect element, such as a few millimetres from demand position. As is_down now is false the variable t_open is increased by 10 ms, which makes the piston move a little bit further down next cycle; this is then considered to be the final position at which the update procedure stops (since the variable adjust is set to false it cannot become true again).
  • This setting will be used for the rest of the treatment or may be changed after some time such as, for instance, 10 minutes from start, to adapt the compression to the aforementioned change in physical properties of the chest.
  • a block diagram of the program is shown in FIG. 3 .
  • the effect of the method of the invention in the control of compressed driving gas is demonstrated by three experiments illustrated in FIGS. 5 a - 5 c .
  • the experiments were carried out with an air-driven reciprocating CPR device mounted on a test bench.
  • the CPR apparatus comprises a compression cylinder 208 comprising an upper compartment 219 and a lower compartment 220 delimited in respect of each other by a piston 216 arranged displaceably in the cylinder 208 .
  • the apparatus further comprises a breast compression pad 210 attached to the piston 216 via a shaft 211 , a valve control unit 212 with a valve manifold, and a gas line 213 supplying driving gas from source of compressed gas (not shown) to the compression cylinder via the valve control unit 212 .
  • the stroke (str) of the piston 216 is limited to 55 mm by means of upper 217 and lower 218 stroke limiters disposed in the upper and lower compartments, 219 , 220 , respectively.
  • the gas pressure in the upper compartment 219 is measured by a manometer 214 .
  • the test bench comprises a flat base 201 on which the CPR apparatus is mounted via a pair of legs 209 .
  • the compression pad 210 abuts a top face of a sternal plate 204 resting on a support 202 via an interposed force sensor 203 .
  • the support 202 rests displaceable in a vertical direction on the base 201 via compression coil means 205 , which mimic a resilient chest.
  • a linear sliding rail 206 fixed at the base 201 allows to read the position of the sternal plate 204 and the compression pad 210 by means of a linear slide guide 207 running on the rail 206 .
  • the slide guide 207 comprises a position sensor.
  • signals from the force sensor 203 , the position sensor 207 , the valve control unit 212 and the manometer 214 are electrically transferred to a control unit 215 in which they are stored and from which the can be recalled and displayed.
  • the resisting force of the compression coil means 205 against further compression at a Compression Depth of about 50 mm was set to about 500 N ( FIG.
  • FIG. 5 a reflects the situation at the start of CPR, that is, during the first compressions administered to a patient.
  • full compression that is, a Compression Depth of about 50 mm for the average adult person, right from start and at an adequate rate of about 100 compressions per minute and even more.
  • the minimum pressure of the driving gas is set to about 3 bar or more. This suffices to develop a compression force of about 500 (477 N in the experiment), by which the compression coil means 205 are compressed to a full stroke (str, FIG. 6 ), the lower stroke limiter 218 being reached at point L in FIG. 5 a.
  • FIG. 5 b reflects the situation after provision of compressions to a patient for a few minutes. During this time period the resistance of the chest diminishes by about 50%. The force of compression necessary to obtain a desired Compression Depth of about 50 mm thus is substantially reduced.
  • the resistance of the compression coil means 205 is set to about half (239 N) of the resistance in experiment (a). A compression profile similar to that of experiment (a) is obtained, except for the downward stroke occurring considerably faster, the lower stroke limiter 218 being reached at M.
  • the driving gas inlet valve is open during the entire compression phase.
  • FIG. 5 c substantially the same time v, compression pad displacement curve is obtained as in experiment (b).
  • Experiment (c) differs from experiment (b) only in that the valve by which driving gas is adduced to the upper chamber 219 is kept open for a comparatively short time only. It is made to close at N ( FIG. 6 ) even before the Compression Depth is reached. The final or maximum gas pressure in the compression compartment is thereby limited to about half of the pressure in experiment (b), and a corresponding saving of driving gas is obtained.

Landscapes

  • Health & Medical Sciences (AREA)
  • Cardiology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Emergency Medicine (AREA)
  • Pulmonology (AREA)
  • Epidemiology (AREA)
  • Pain & Pain Management (AREA)
  • Physical Education & Sports Medicine (AREA)
  • Rehabilitation Therapy (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Percussion Or Vibration Massage (AREA)
US12/523,082 2007-01-18 2008-01-14 Driving control of a reciprocating cpr apparatus Abandoned US20100004571A1 (en)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
SE07000094-6 2007-01-18
SE0700094 2007-01-18
PCT/SE2008/000022 WO2008088267A1 (en) 2007-01-18 2008-01-14 Driving control of a reciprocating cpr apparatus

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
PCT/SE2008/000022 A-371-Of-International WO2008088267A1 (en) 2007-01-18 2008-01-14 Driving control of a reciprocating cpr apparatus

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US13/549,164 Division US9844487B2 (en) 2007-01-18 2012-07-13 Driving control of a reciprocating CPR apparatus

Publications (1)

Publication Number Publication Date
US20100004571A1 true US20100004571A1 (en) 2010-01-07

Family

ID=39636193

Family Applications (4)

Application Number Title Priority Date Filing Date
US12/523,082 Abandoned US20100004571A1 (en) 2007-01-18 2008-01-14 Driving control of a reciprocating cpr apparatus
US13/549,164 Active 2030-10-08 US9844487B2 (en) 2007-01-18 2012-07-13 Driving control of a reciprocating CPR apparatus
US15/842,638 Active 2029-04-06 US10821051B2 (en) 2007-01-18 2017-12-14 Driving control of a reciprocating CPR apparatus
US17/085,026 Active 2029-09-02 US11850209B2 (en) 2007-01-18 2020-10-30 Driving control of a reciprocating CPR apparatus

Family Applications After (3)

Application Number Title Priority Date Filing Date
US13/549,164 Active 2030-10-08 US9844487B2 (en) 2007-01-18 2012-07-13 Driving control of a reciprocating CPR apparatus
US15/842,638 Active 2029-04-06 US10821051B2 (en) 2007-01-18 2017-12-14 Driving control of a reciprocating CPR apparatus
US17/085,026 Active 2029-09-02 US11850209B2 (en) 2007-01-18 2020-10-30 Driving control of a reciprocating CPR apparatus

Country Status (3)

Country Link
US (4) US20100004571A1 (de)
EP (2) EP2599468A1 (de)
WO (1) WO2008088267A1 (de)

Cited By (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20140052032A1 (en) * 2012-08-17 2014-02-20 Zoll Medical Corporation Out of Phase Chest Compression and Ventilation
US20140066822A1 (en) * 2012-09-06 2014-03-06 Zoll Medical Corporation Method and Device for Mechanical Chest Compression with Optical Alignment
US20140066860A1 (en) * 2012-08-28 2014-03-06 Osprey Medical, Inc. Volume monitoring device
WO2014051933A1 (en) * 2012-09-27 2014-04-03 Zoll Medical Corporation Mechanical chest compression plunger adapter and compression pad
US20140148744A1 (en) * 2011-07-14 2014-05-29 Cizeta Medicali S.P.A. Roller device for lymphatic drainage treatments
US20140171840A1 (en) * 2011-08-26 2014-06-19 Koninklijke Philips Electronics N.V. Cardio pulmonary resuscitation device with means for initial setup
US20140180180A1 (en) * 2012-12-21 2014-06-26 Physio-Control, Inc. Mechanical cpr device with automatic suction cup attachment
CN104755058A (zh) * 2012-09-28 2015-07-01 佐尔医药公司 用于执行交替的胸部压缩和减压的方法与装置
CN104905954A (zh) * 2015-07-02 2015-09-16 上海尚领医疗科技有限公司 一种电控气动心肺复苏装置
US20150272818A1 (en) * 2012-08-14 2015-10-01 Schiller Ag Apparatus for assisting cardiopulmonary resuscitation and method for operating the apparatus
US9320678B2 (en) 2013-09-30 2016-04-26 Zoll Circulation, Inc. Chest compression device
US9566210B2 (en) 2010-11-11 2017-02-14 Koninklijke Philips N.V. Chest following algorithm for automated CPR device
US20170119623A1 (en) * 2014-05-29 2017-05-04 Resuscitation International, Llc Electromechanical chest compression system and method
US20170156977A1 (en) * 2013-11-25 2017-06-08 Koninklijke Philips N.V. Compensation for deflection in an automated cardiopulmonary compression device
US20190175443A1 (en) * 2016-08-03 2019-06-13 Jolife Ab Mechanical cpr with selective zero-position & compression depth adjustment
CN110547960A (zh) * 2019-10-17 2019-12-10 苏州尚领医疗科技有限公司 一种可透射x线的心肺复苏按压器
US10639234B2 (en) 2015-10-16 2020-05-05 Zoll Circulation, Inc. Automated chest compression device
US10682282B2 (en) 2015-10-16 2020-06-16 Zoll Circulation, Inc. Automated chest compression device
US10874583B2 (en) 2017-04-20 2020-12-29 Zoll Circulation, Inc. Compression belt assembly for a chest compression device
US10905629B2 (en) 2018-03-30 2021-02-02 Zoll Circulation, Inc. CPR compression device with cooling system and battery removal detection
US20210106495A1 (en) * 2019-10-15 2021-04-15 Koninklijke Philips N.V. Apparatus for generating a reciprocating rotary motion
US11116892B2 (en) 2012-08-28 2021-09-14 Osprey Medical, Inc. Medium injection diversion and measurement
US11135375B2 (en) 2012-08-28 2021-10-05 Osprey Medical, Inc. Volume monitoring systems
US11179293B2 (en) 2017-07-28 2021-11-23 Stryker Corporation Patient support system with chest compression system and harness assembly with sensor system
US11246795B2 (en) 2017-04-20 2022-02-15 Zoll Circulation, Inc. Compression belt assembly for a chest compression device
US20220323297A1 (en) * 2021-04-07 2022-10-13 The Government of the United States of America, as represented by the Secretary of Homeland Security Remote modular system for delivering cpr compression
US11499841B2 (en) 2019-04-12 2022-11-15 Osprey Medical, Inc. Energy-efficient position determining with multiple sensors

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101788793B (zh) * 2009-08-21 2013-11-13 河南迈松医用设备制造有限公司 一种按压深度精确调节的心肺复苏机传感控制装置
US8942803B1 (en) 2013-08-30 2015-01-27 Zoll Medical Corporation System and method for distinguishing manual from automated CPR
US10832594B2 (en) 2017-03-09 2020-11-10 Zoll Medical Corporation Automated detection of cardiopulmonary resuscitation chest compressions
US11311457B2 (en) 2017-03-09 2022-04-26 Zoll Medical Corporation Automated detection of cardiopulmonary resuscitation chest compressions
DE102017115732A1 (de) * 2017-07-13 2019-01-17 GS Elektromedizinische Geräte G. Stemple GmbH Vorrichtung zur kardiopulmonalen Massage und/oder Reanimation
CN108652944A (zh) * 2018-05-23 2018-10-16 李云祥 一种心肺复苏抢救机

Citations (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3209747A (en) * 1963-03-19 1965-10-05 Westinghouse Electric Corp Heart resuscitation apparatus with means for quickly adjusting to the size of the patient
US3277887A (en) * 1963-11-21 1966-10-11 Westinghouse Electric Corp Portable heart massage apparatus
US3364924A (en) * 1964-11-09 1968-01-23 Michigan Instr Inc Pneumatically operated closed chest cardiac compressor
US4471656A (en) * 1983-02-11 1984-09-18 Oil Recovery Systems, Inc. Apparatus for fluid mass measurement
US6030353A (en) * 1998-04-28 2000-02-29 American Biosystems, Inc. Pneumatic chest compression apparatus
US6171267B1 (en) * 1999-01-07 2001-01-09 Michigan Instruments, Inc. High impulse cardiopulmonary resuscitator
US20030181834A1 (en) * 2002-03-21 2003-09-25 Jolife Ab Support structure
US20040230140A1 (en) * 2003-05-12 2004-11-18 Stig Steen Systems and procedures for treating cardiac arrest
US20050058977A1 (en) * 2003-09-12 2005-03-17 Bearco, Llc CPR training device
US20060087313A1 (en) * 2004-10-27 2006-04-27 Deere & Company, A Delaware Corporation. System and method for detecting the axial position of a shaft or a member attached thereto
US7118542B2 (en) * 2002-10-25 2006-10-10 Zoll Circulation, Inc. Devices for determining depth of chest compressions during CPR
US20070270724A1 (en) * 2006-05-11 2007-11-22 Laerdal Medical As Servo motor for cpr
US20070276300A1 (en) * 2006-05-26 2007-11-29 Olson Kenneth F Cpr feedback method and apparatus
US7517325B2 (en) * 1998-11-09 2009-04-14 The Johns Hopkins University Automated chest compression apparatus with a bladder between the belt and the patient

Family Cites Families (21)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3779672A (en) * 1970-03-03 1973-12-18 W Schroeder Air compressor
US4273114A (en) * 1978-10-19 1981-06-16 Michigan Instruments, Inc. Cardiopulmonary resuscitator, defibrillator and monitor
US4343597A (en) * 1980-04-11 1982-08-10 Facet Enterprises, Inc. Reciprocating fluid pump having a hall switch
US4726366A (en) * 1986-04-18 1988-02-23 Life Products, Incorporated Apparatus and method for controlling lung ventilation
DE3735066A1 (de) * 1987-10-16 1989-04-27 Bochumer Eisen Heintzmann Drucksensor
GB9720911D0 (en) * 1997-10-03 1997-12-03 Britax Rainsfords Pty Ltd Hall effect sensor system
US6155257A (en) * 1998-10-07 2000-12-05 Cprx Llc Cardiopulmonary resuscitation ventilator and methods
US7886610B2 (en) * 1999-07-19 2011-02-15 Donaldson Company, Inc. Differential pressure gauge for filter
TW407053B (en) * 2000-01-21 2000-10-01 Jang Ting Tsai Automatic inflation cardiopulmonary resuscitation apparatus with both electric and manual operation modes
DE10013196B4 (de) * 2000-03-17 2004-02-26 Festo Ag & Co. Positionserfassungseinrichtung
US6690159B2 (en) * 2000-09-28 2004-02-10 Eldec Corporation Position indicating system
WO2002091905A2 (en) * 2001-05-11 2002-11-21 Advanced Circulatory Systems, Inc. Cardiopulmonary resuscitation chest compression/decompression device with electronic stethoscope
US6652039B1 (en) * 2002-09-30 2003-11-25 Robert Bosch Corporation Anti-lock braking system with accumulator volume monitoring
US7221151B2 (en) * 2003-01-31 2007-05-22 Delphi Technologies, Inc. Magnetic array position sensor
US8795208B2 (en) * 2004-11-03 2014-08-05 Physio-Control, Inc. Mechanical CPR device with variable resuscitation protocol
US7805191B2 (en) * 2005-01-31 2010-09-28 Physio-Control, Inc. CPR time indicator for a defibrillator data management system
US7127982B2 (en) * 2005-03-04 2006-10-31 Festo Corporation Linear drive with non-rotating piston
US8105249B2 (en) * 2006-02-16 2012-01-31 Zoll Medical Corporation Synchronizing chest compression and ventilation in cardiac resuscitation
US7775996B2 (en) * 2006-10-20 2010-08-17 Laerdal Medical As Chest compression system
CN102084445A (zh) * 2008-05-19 2011-06-01 石通瑞吉控制装置公司 汽缸位置传感器和包括所述传感器的汽缸
GB0812903D0 (en) * 2008-07-15 2008-08-20 Rota Eng Ltd Linear actuator and position sensing apparatus therefor

Patent Citations (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3209747A (en) * 1963-03-19 1965-10-05 Westinghouse Electric Corp Heart resuscitation apparatus with means for quickly adjusting to the size of the patient
US3277887A (en) * 1963-11-21 1966-10-11 Westinghouse Electric Corp Portable heart massage apparatus
US3364924A (en) * 1964-11-09 1968-01-23 Michigan Instr Inc Pneumatically operated closed chest cardiac compressor
US4471656A (en) * 1983-02-11 1984-09-18 Oil Recovery Systems, Inc. Apparatus for fluid mass measurement
US6030353A (en) * 1998-04-28 2000-02-29 American Biosystems, Inc. Pneumatic chest compression apparatus
US7517325B2 (en) * 1998-11-09 2009-04-14 The Johns Hopkins University Automated chest compression apparatus with a bladder between the belt and the patient
US6171267B1 (en) * 1999-01-07 2001-01-09 Michigan Instruments, Inc. High impulse cardiopulmonary resuscitator
US20030181834A1 (en) * 2002-03-21 2003-09-25 Jolife Ab Support structure
US7118542B2 (en) * 2002-10-25 2006-10-10 Zoll Circulation, Inc. Devices for determining depth of chest compressions during CPR
US7226427B2 (en) * 2003-05-12 2007-06-05 Jolife Ab Systems and procedures for treating cardiac arrest
US20040230140A1 (en) * 2003-05-12 2004-11-18 Stig Steen Systems and procedures for treating cardiac arrest
US20050058977A1 (en) * 2003-09-12 2005-03-17 Bearco, Llc CPR training device
US20060087313A1 (en) * 2004-10-27 2006-04-27 Deere & Company, A Delaware Corporation. System and method for detecting the axial position of a shaft or a member attached thereto
US20070270724A1 (en) * 2006-05-11 2007-11-22 Laerdal Medical As Servo motor for cpr
US20070276300A1 (en) * 2006-05-26 2007-11-29 Olson Kenneth F Cpr feedback method and apparatus

Cited By (50)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9566210B2 (en) 2010-11-11 2017-02-14 Koninklijke Philips N.V. Chest following algorithm for automated CPR device
US20140148744A1 (en) * 2011-07-14 2014-05-29 Cizeta Medicali S.P.A. Roller device for lymphatic drainage treatments
US20140171840A1 (en) * 2011-08-26 2014-06-19 Koninklijke Philips Electronics N.V. Cardio pulmonary resuscitation device with means for initial setup
US20150272818A1 (en) * 2012-08-14 2015-10-01 Schiller Ag Apparatus for assisting cardiopulmonary resuscitation and method for operating the apparatus
US11974961B2 (en) 2012-08-17 2024-05-07 Zoll Medical Corporation Out of phase chest compression and ventilation
US10888493B2 (en) 2012-08-17 2021-01-12 Zoll Medical Corporation Out of phase chest compression and ventilation
US20140052032A1 (en) * 2012-08-17 2014-02-20 Zoll Medical Corporation Out of Phase Chest Compression and Ventilation
US10188582B2 (en) * 2012-08-17 2019-01-29 Zoll Medical Corporation Out of phase chest compression and ventilation
US11135375B2 (en) 2012-08-28 2021-10-05 Osprey Medical, Inc. Volume monitoring systems
US20140066860A1 (en) * 2012-08-28 2014-03-06 Osprey Medical, Inc. Volume monitoring device
US11116892B2 (en) 2012-08-28 2021-09-14 Osprey Medical, Inc. Medium injection diversion and measurement
US11219719B2 (en) 2012-08-28 2022-01-11 Osprey Medical, Inc. Volume monitoring systems
US10413677B2 (en) * 2012-08-28 2019-09-17 Osprey Medical, Inc. Volume monitoring device
WO2014039383A1 (en) * 2012-09-06 2014-03-13 Zoll Medical Corporation Method and device for mechanical chest compression with optical alignment
US8808205B2 (en) * 2012-09-06 2014-08-19 Zoll Medical Corporation Method and device for mechanical chest compression with optical alignment
US20140066822A1 (en) * 2012-09-06 2014-03-06 Zoll Medical Corporation Method and Device for Mechanical Chest Compression with Optical Alignment
CN104717951A (zh) * 2012-09-06 2015-06-17 佐尔医药公司 具有光学校准的用于机械胸部按压的方法和装置
US8888725B2 (en) 2012-09-27 2014-11-18 Zoll Medical Corporation Mechanical chest compression plunger adapter and compression pad
WO2014051933A1 (en) * 2012-09-27 2014-04-03 Zoll Medical Corporation Mechanical chest compression plunger adapter and compression pad
CN104755058A (zh) * 2012-09-28 2015-07-01 佐尔医药公司 用于执行交替的胸部压缩和减压的方法与装置
US20140180180A1 (en) * 2012-12-21 2014-06-26 Physio-Control, Inc. Mechanical cpr device with automatic suction cup attachment
US9713568B2 (en) * 2012-12-21 2017-07-25 Physio-Control, Inc. Mechanical CPR device with automatic suction cup attachment
US10792215B2 (en) 2012-12-21 2020-10-06 Physio-Control, Inc. Mechanical CPR device
US10166169B2 (en) 2013-09-30 2019-01-01 Zoll Circulation, Inc. Chest compression device
US11554075B2 (en) 2013-09-30 2023-01-17 Zoll Circulation, Inc. Chest compression device
US10695265B2 (en) 2013-09-30 2020-06-30 Zoll Circulation, Inc. Chest compression device
US9320678B2 (en) 2013-09-30 2016-04-26 Zoll Circulation, Inc. Chest compression device
US20170156977A1 (en) * 2013-11-25 2017-06-08 Koninklijke Philips N.V. Compensation for deflection in an automated cardiopulmonary compression device
US10751247B2 (en) * 2013-11-25 2020-08-25 Koninklijke Philips N.V. Compensation for deflection in an automated cardiopulmonary compression device
US20170119623A1 (en) * 2014-05-29 2017-05-04 Resuscitation International, Llc Electromechanical chest compression system and method
CN104905954A (zh) * 2015-07-02 2015-09-16 上海尚领医疗科技有限公司 一种电控气动心肺复苏装置
US10682282B2 (en) 2015-10-16 2020-06-16 Zoll Circulation, Inc. Automated chest compression device
US11723833B2 (en) 2015-10-16 2023-08-15 Zoll Circulation, Inc. Automated chest compression device
US11666506B2 (en) 2015-10-16 2023-06-06 Zoll Circulation, Inc. Automated chest compression device
US10639234B2 (en) 2015-10-16 2020-05-05 Zoll Circulation, Inc. Automated chest compression device
US20190175443A1 (en) * 2016-08-03 2019-06-13 Jolife Ab Mechanical cpr with selective zero-position & compression depth adjustment
US11813224B2 (en) 2017-04-20 2023-11-14 Zoll Circulation, Inc. Compression belt assembly for a chest compression device
US10874583B2 (en) 2017-04-20 2020-12-29 Zoll Circulation, Inc. Compression belt assembly for a chest compression device
US11246795B2 (en) 2017-04-20 2022-02-15 Zoll Circulation, Inc. Compression belt assembly for a chest compression device
US11179293B2 (en) 2017-07-28 2021-11-23 Stryker Corporation Patient support system with chest compression system and harness assembly with sensor system
US11723835B2 (en) 2017-07-28 2023-08-15 Stryker Corporation Patient support system with chest compression system and harness assembly with sensor system
US10905629B2 (en) 2018-03-30 2021-02-02 Zoll Circulation, Inc. CPR compression device with cooling system and battery removal detection
US11499841B2 (en) 2019-04-12 2022-11-15 Osprey Medical, Inc. Energy-efficient position determining with multiple sensors
US20210106495A1 (en) * 2019-10-15 2021-04-15 Koninklijke Philips N.V. Apparatus for generating a reciprocating rotary motion
US11951065B2 (en) * 2019-10-15 2024-04-09 Koninklijke Philips N.V. Apparatus for generating a reciprocating rotary motion
CN110547960A (zh) * 2019-10-17 2019-12-10 苏州尚领医疗科技有限公司 一种可透射x线的心肺复苏按压器
US11701296B2 (en) * 2021-04-07 2023-07-18 The Government of the United States of America, as represented by the Secretary of Homeland Security Remote modular system and method for delivering cpr compression
US20230157926A1 (en) * 2021-04-07 2023-05-25 The Government of the United States of America, as represented by the Secretary of Homeland Security Remote modular system and method for delivering cpr compression
US11607368B2 (en) * 2021-04-07 2023-03-21 The Government of the United States of America, as represented by the Secretary of Homeland Security Remote modular system for delivering CPR compression
US20220323297A1 (en) * 2021-04-07 2022-10-13 The Government of the United States of America, as represented by the Secretary of Homeland Security Remote modular system for delivering cpr compression

Also Published As

Publication number Publication date
US9844487B2 (en) 2017-12-19
US10821051B2 (en) 2020-11-03
US20120283608A1 (en) 2012-11-08
US11850209B2 (en) 2023-12-26
US20180168924A1 (en) 2018-06-21
US20210045969A1 (en) 2021-02-18
EP2107901A1 (de) 2009-10-14
WO2008088267A1 (en) 2008-07-24
EP2107901A4 (de) 2012-11-28
EP2599468A1 (de) 2013-06-05

Similar Documents

Publication Publication Date Title
US9844487B2 (en) Driving control of a reciprocating CPR apparatus
US6155257A (en) Cardiopulmonary resuscitation ventilator and methods
US6962599B2 (en) High efficiency external counterpulsation apparatus and method for controlling same
US7354410B2 (en) Compression treatment system
EP2314268B1 (de) Kompressionsbehandlungssystem
US20100198118A1 (en) Augmenting force-delivery in belt-type ECM devices
US5327887A (en) Cardiopulmonary resuscitation device
AU740070B2 (en) External blood pressure sensor apparatus and method
US10201474B2 (en) Method and apparatus for improved ventilation and cardio-pulmonary resuscitation
CN109044472B (zh) 一种心内科用智能按压止血装置
US20050148909A1 (en) Light weight chest compressor
US20140135668A1 (en) Cardio-pulmonary resuscitation airway valve and devices
US20220142859A1 (en) A time saving sit on cardio pulmonary resuscitation device and method
US20130018291A1 (en) Apparatus for facilitating circulation
US7811318B2 (en) Apparatus and method for pneumatically driving an implantable medical device
US20050015026A1 (en) Controlled chest compressor
KR102482081B1 (ko) 혈압을 측정하기 위한 가이드를 제공하는 마사지 장치
KR102466440B1 (ko) 흉부 임피던스를 이용한 심폐소생술장치 및 자동심장충격기 융합 시스템
CN109199839A (zh) 一种心肺复苏按压系统、心肺复苏仪及医疗架
KR102570693B1 (ko) 방사선 치료용 호흡 모니터링 장치
US20220151867A1 (en) Cardiopulmonary resuscitation system
EP2698141A1 (de) Vorrichtung zum Unterstützen der cardiopulmonalen Wiederbelebung
JPH03280969A (ja) 大動脈内バルーン駆動制御装置

Legal Events

Date Code Title Description
AS Assignment

Owner name: JOLIFE AB, SWEDEN

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:NILSSON, ANDERS;SEBELIUS, PETER;REEL/FRAME:023097/0455;SIGNING DATES FROM 20090626 TO 20090803

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION

AS Assignment

Owner name: PHYSIO-CONTROL, INC., WASHINGTON

Free format text: STATEMENT OF ASSIGNMENT;ASSIGNOR:JOLIFE AB;REEL/FRAME:036010/0454

Effective date: 20121015