EP1089701B1 - Dispositif de compression intermittente - Google Patents

Dispositif de compression intermittente Download PDF

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Publication number
EP1089701B1
EP1089701B1 EP99938212A EP99938212A EP1089701B1 EP 1089701 B1 EP1089701 B1 EP 1089701B1 EP 99938212 A EP99938212 A EP 99938212A EP 99938212 A EP99938212 A EP 99938212A EP 1089701 B1 EP1089701 B1 EP 1089701B1
Authority
EP
European Patent Office
Prior art keywords
cuff
pressure
set forth
outlet
pump
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.)
Expired - Lifetime
Application number
EP99938212A
Other languages
German (de)
English (en)
Other versions
EP1089701A2 (fr
Inventor
Hans R. Brunner
Daniel Hayoz
Beat Steffen
Ueli Haueter
Andreas Schaer
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.)
BMRA Corp BV
B M R A Corp BV
Original Assignee
BMRA Corp BV
B M R A Corp BV
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 BMRA Corp BV, B M R A Corp BV filed Critical BMRA Corp BV
Publication of EP1089701A2 publication Critical patent/EP1089701A2/fr
Application granted granted Critical
Publication of EP1089701B1 publication Critical patent/EP1089701B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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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
    • A61H9/00—Pneumatic or hydraulic massage
    • A61H9/005—Pneumatic massage
    • A61H9/0078—Pneumatic massage with intermittent or alternately inflated bladders or cuffs

Definitions

  • the present invention relates to a device for intermittent compression of human extremities, which is suitable for use as a portable device in everyday situations.
  • Devices for the intermittent compression of human extremities are used to treat or treat venous diseases or disorders.
  • Use using a cuff that is placed around the extremity to be treated, intermittently, i. H. with interruptions, pressure exerted on the extremity is built up and reduced again.
  • the extremity to be treated is usually completely inserted into a large-volume unicameral system, which is then rhythmically pressurized.
  • Such a device is known from DE 704 510.
  • Devices used today are based on the multi-chamber principle, in which a plurality of cuff chambers are pressurized sequentially from distal to proximal along the extremity to be treated, in order to support the return transport of body fluid towards the heart. It is also known to design a multi-chamber system in such a way that the return transport is supported by a pressure wave constantly sliding along the extremity.
  • a portable pump device for a multi-chamber system is known from EP 0 329 470 A2.
  • a compression chamber with outlets is proposed, the number of which corresponds to the number of cuff chambers, the same number of valves in the compression chamber being operated sequentially by means of a camshaft.
  • US 5,634,889 discloses a device for intermittent compression of a body tissue in the area of a joint, e.g. To reduce swelling of the joint.
  • a cuff is provided with an inflatable body which can be inflated by a pump via a hose.
  • EP 0 542 413 A1 discloses a patient monitoring system with a blood pressure measuring unit for the regular measurement of blood pressure.
  • the invention can be used in everyday situations to promote physical well-being, in particular to support thrombosis prophylaxis, to support the return transport of lymphatic fluid, to relieve stress, to massage and more generally to promote physical well-being.
  • the invention is defined in claim 1 and relates to a device for intermittent compression, which comprises a cuff to be applied to an extremity and a pressure generator for pressurizing the cuff.
  • the invention is based on the knowledge gained in medical test series that intermittent compression even from comparatively small areas of the body has a surprisingly advantageous effect on the human organism and supports, for example, thrombosis prophylaxis.
  • the cuff points in the direction of the return transport of the body fluid, ie. H. from distal to proximal, a width of not more than 25 cm, preferably a width of at least 5 cm, preferably at least 8 cm and at most 20 cm, preferably at most 18 cm.
  • the incredibly simple device is ideal for self-treatment without the need for therapeutic use or even a doctor's prescription. It can be put on and started in just a few simple steps. Supervision by medical professionals is not required; just as little instruction.
  • the cuff is preferably placed in the manner of a cuff for measuring the blood pressure .mu.m of the limb to be treated and then suitably tightened by means of a closure.
  • a pump is used as the pressure generator, preferably the compressed air generator.
  • a pressurized fluid reservoir such as a pressurized fluid can, can also be used.
  • the pressure generator including any associated power supply is attached directly to the cuff.
  • the connecting line can comprise a quick-connect connection or coupling, such as a bayonet coupling.
  • the device Due to its small dimensions, the device can be easily transported and thus in everyday situations, for example at the desk, on the go in the car or on air travel, i.e. be used for long periods of sitting, but also for long standing activities. Due to a simple construction from only a few simple components, the device according to the invention is light, simple, robust and inexpensive to handle, purchase, maintain and operate. The device is particularly suitable for self-treatment by the user himself, for example in thromboprophylaxis and as a wellness device for reducing stress.
  • the cuff chamber is designed as a unicameral system, which includes the case that the cuff chamber, in the longitudinal and / or transverse direction, is divided into several segments which, depending on the dimensioning of the segment connections, are pressurized in a defined order or at the same time and preferably uniformly.
  • a cuff of the type used for measuring blood pressure can advantageously be used. Since the cuff according to the invention can thus be a standard product which is inexpensive and can be obtained in large numbers, the outlay for producing and operating the device according to the invention is reduced. Furthermore, the procurement of spare parts is much easier if the chamber should leak. A blood pressure measuring cuff which may already be present in the user can also be used in a simple manner at very low cost within the scope of the invention.
  • a diaphragm pump which is available in very small dimensions and inexpensively, is preferably used as the pump. Basically, others can Miniature pumps can be used.
  • the pump is supplied independently of the mains by means of a commercially available small battery, preferably a small rechargeable battery, which further improves the mobile use of the device in everyday situations.
  • a device operated in a network-dependent manner or a device which can be operated in a network-independent and network-dependent manner likewise form embodiments according to the invention.
  • the device comprises a pressure control device with, for example, an electromechanical outlet valve which is connected to the environment in order to suitably control or simply limit the pressure in the cuff in a predetermined manner.
  • the valve can be an integral part of the pump.
  • a control unit for example in the form of a microprocessor or an application-specific circuit (ASIC), is provided, which includes a timer and is also powered by the voltage supply to the pump.
  • the control unit provides a suitable timing control for switching the pump on and off and for actuating the outlet valve.
  • the pressure control device can comprise a pressure sensor, the output signal of which is fed to the control unit which, when a target pressure is exceeded, controls the outlet valve for the pressure release.
  • a signal derived from the motor current of the pump can alternatively be used as the control variable for pressure control, which signal also changes with increasing back pressure in the cuff chamber.
  • the pressure control is preferably carried out in such a way that the pump is turned on for a short time to build up pressure and the outlet valve is blocked. After the predetermined pressure has built up in the chamber, the pump is switched off and the outlet valve is opened after a time which can be changed until the pump is switched on again for the next pump cycle.
  • the frequency and duration of the pressure build-up are preferably specified with the aid of a fixed program, and a selection function between several fixed programs can be provided for the user.
  • the maximum pressure or the repetition frequency or both can be adapted individually or in predetermined combinations by the user within predetermined limits to his own needs.
  • the outlet valve is preferably open in its rest position, which ensures particularly safe operation of the device.
  • the outlet valve is designed purely mechanically, and an integrated pressure sensor can be provided.
  • This pressure control device has an outlet valve with a shut-off body, which in a first position, preferably its rest position, releases an outlet to the environment so that the excess pressure can escape from the cuff chamber into the environment, and in a second position blocks the outlet so that it is closed an excess pressure can build up in the cuff chamber when the pump is actuated.
  • a delayed build-up of pressure in the cuff chamber relative to the pump outlet pressure is preferably used to control the outlet valve.
  • a throttle is preferably provided in a flow cross section between the pump and the sleeve.
  • the shut-off body is preferably a flexible membrane which separates a first chamber from a second chamber and blocks or opens the outlet.
  • the first chamber is connected to a throttle inlet and the second chamber is connected to a throttle outlet and has the outlet to the surroundings. If the pump is switched on, the faster build-up of pressure in the first chamber and the resulting pressure difference between the two chambers result in an adjustment of the shut-off body, which blocks the outlet and builds up excess pressure in the cuff.
  • the pressure control can consequently only comprise a simple timer which switches the pump on and off at predetermined time intervals.
  • the chamber of the cuff is preferably subjected to a pressure between about 20 and 100 mm Hg, preferably in a range between 25 and 80 mm Hg and in particular between 40 and 60 mm Hg.
  • the pressure is released within 1 to 10 seconds and preferably within 2 to 5 seconds built up and then quickly, for example in a maximum of 5 seconds, preferably in a maximum of 3 seconds and in particular within a maximum of 1 second, degraded.
  • the pump is actuated between 1 and 15 times per 5 minutes and preferably between 1 and 5 times per minute.
  • the device according to the invention can be carried along by the user at all times and can be put on as needed, for example at the workplace, on the go while traveling, even at home in front of the television or while sleeping. It can be used completely inconspicuously.
  • the high availability makes effective thrombosis prophylaxis possible without therapeutic measures.
  • Figure 1 shows a device according to the invention.
  • This comprises a pump 1 with an inlet 7 to the environment and a cuff 2 with an inflatable chamber which is placed around a human extremity, in particular in a calf area.
  • the pump 1 is connected via a connecting line 6 to the sleeve 2, the length of which depends on the type of mounting of the pump 1 and is kept as short as possible.
  • the cuff 2 is designed in the manner of a cuff known from blood pressure measurement. It can have a textile cover in order to avoid any skin irritation.
  • the cuff 2 is provided with a bow 9 for pulling through and folding over and a Velcro fastener 8 such that it can be placed either on the left or right leg. In the unrolled state, the area of the sleeve 2 forming the chamber has a simple rectangular shape.
  • the cuff 2 has an effective width B of between 5 cm and 25 cm, preferably between 8 and 20 cm; in the exemplary embodiment it is 15 cm wide.
  • the effective width of the cuff 2, i.e. H. the printable width is, in good approximation, equal to the total width of the sleeve 2.
  • a control unit 5 with a microprocessor and a timer controls the pump 1 according to a predetermined program.
  • a pressure control device comprising the control unit 5 also has a controlled electromechanical outlet valve 3 for releasing air from the cuff chamber into the environment and a pressure sensor 4 for measuring the cuff chamber pressure, expediently a capacitive pressure sensor or a semiconductor strain gauge in a Wheatstone bridge circuit, each of which are connected to the control unit 5.
  • the outlet valve and also the pressure sensor can be integrated in the sleeve 2.
  • the pressure is controlled by the control unit 5. In a more complex configuration, a pressure control could also be provided.
  • the cuff 2 as such forms the printable chamber, so that no edge seal to the wrapped surface is required.
  • the cuff 2 with the pump 1 and the necessary connections is thus a closed pressure system when the outlet valve is closed.
  • Figure 2 shows, plotted against time, the activation of the pump and the pressure prevailing in the inflatable chamber of the cuff.
  • the pump 1 In order to pressurize the inflatable chamber of the cuff 2, the pump 1, as shown in the lower part of FIG. 2, is switched on during a time interval t 2 .
  • This time interval is preferably about 2 to 10 seconds.
  • the outlet to the environment is blocked via the outlet valve 3.
  • the outlet valve 3 When the pump 1 is switched off, the outlet valve 3 either releases the outlet immediately or only after a short delay. The release can also take place as a function of an output signal of the pressure sensor 4 or of a signal corresponding to the size of the motor current. After the release, the excess pressure in the cuff chamber decreases again approximately to the ambient pressure during a time interval t 3 .
  • This time interval is preferably shorter than the time interval t 2 , which is ensured by the design of the flow cross sections under consideration.
  • the pump 1 is actuated again, as a result of which an excess pressure builds up again in the cuff chamber according to the above procedure.
  • This cycle is preferably repeated between one and five times per 5 minutes in accordance with the programming of the control unit 5.
  • the cuff chamber communicates with the surroundings via the outlet valve 3, so that the outlet valve 3 is only actively activated during the comparatively short time interval t 2 .
  • the inflatable chamber of the cuff 2 can be segmented in length and / or width so that it adapts better to the extremity.
  • the chamber as a whole is designed as a single-chamber system, so that a uniform pressure is formed in the several chamber segments.
  • the pump is a diaphragm pump, such as that manufactured by OKEN SEIKO CO., LTD., TOKYO, Japan, in the types P23B, P23E, P36B or P36C. Preferred characteristics are: voltage 2-7 V, current 50-400 mA, idle pump power 0.5-2 1 / min.
  • the pump is supplied with a battery or Battery reservoir connected (mains-independent operation); In addition or instead, a connection option for the external voltage supply can be provided (mains operation).
  • the maximum pump delivery rate is about 0.81 / min with a back pressure P or chamber pressure of 0 mmHg. From this maximum value, the delivery rate Q drops along the characteristic line to the value 0 at a back pressure P of 550 mmHg.
  • the maximum power consumption I occurs at a back pressure P of 200 mmHg and runs over the pump work area along the characteristic curve I entered for this.
  • the pump, the energy source and the pressure control device are accommodated in a box, which is preferably detachably attached directly to the cuff with the aid of a Velcro fastener.
  • the pump is attached to the extremity near the cuff by means of an elastic band with Velcro.
  • the pump is accommodated in an outer pocket formed on the sleeve.
  • the connecting line 6 is a plastic hose which is detachably or permanently connected to the pump or the cuff via a hose transition piece.
  • the connecting line 6 can comprise a bayonet connection, a Velcro coupling or other suitable couplings in order to separate the pump and the cuff from one another, for example for the purpose of an exchange. It can be formed by such couplings themselves.
  • An overpressure between 40 and 60 mm Hg is preferably built up in the cuff chamber.
  • the time interval t 1 is between approximately 1 and 3 minutes.
  • the user can choose between two pressure levels and two repetition frequencies, preferably 40 or 60 mm Hg overpressure and one or five repetitions per minute, the program being selected with the aid of a switch or button.
  • FIG. 4 shows a further embodiment of the device according to the invention, in which a purely mechanical outlet valve with an already integrated pressure sensor is used instead of an electromechanical outlet valve controlled by a control unit.
  • a purely mechanical outlet valve with an already integrated pressure sensor is used instead of an electromechanical outlet valve controlled by a control unit.
  • the same reference numerals indicate the same components that have already been described above.
  • the first sub-chamber 24 communicates with the pump 1 via the connecting section 6a
  • the second sub-chamber 25 communicates with the cuff 2 via the connecting section 6c.
  • the connecting section 6b is through which the sub-chambers 24 and 25 are also connected to one another , narrowed. Section 6b forms a throttle.
  • the shut-off body 22 is designed as an elastic membrane of suitable strength and elasticity, which prevents the short circuit of the cuff 2 and pump 1 via the subchambers 24 and 25.
  • the pump 1 is actuated in accordance with the timing shown qualitatively in the lower part of FIG. Due to the narrowed flow cross section of the connecting section 6b, after the pump 1 is switched on, the pressure in the sub-chamber 24 builds up faster than in the sub-chamber 25 in the time interval t 2. The pressure of the cuff chamber prevails in the sub-chamber 25. Due to the resulting pressure difference across the shut-off body 22, the latter is arched into its first position, to the right in FIG. 4, and blocks the outlet 21.
  • connection section 6b After the connection section 6b, pressure equalization essentially delays with respect to the partial chambers 24 and 25 towards the end of the Time interval t 2 is almost completely completed, the membrane 22 lifts again from the outlet 21 and releases the connection to the environment in order to release the excess pressure built up in the cuff 2 when a predetermined pressure level is reached. This leads to the sigmoid course of the pressure shown in the upper part of FIG. 2 in the time interval t 3 .
  • the pressure control described is effected by prestressing the shut-off body 22 away from the outlet 21, in particular by the choice of the elastic restoring force of the shut-off body.
  • An arrangement of the shut-off body is preferred in which the outlet 21 is released in the installed position of the shut-off body.
  • a ball attached to a flexible partition can also be provided as the shut-off body 22, which is held and blocks the outlet 21 only against the force of a spring.
  • FIG. 5 shows the measured vein diameter and the flow rate
  • FIG. 5 (b) shows the blood flow rate calculated therefrom.
  • a first preferred application relates to the reduction of stress and fatigue. Because in modern professional life activities mainly take place in a seated or statically upright position, the lower leg area (calves, feet) swells over the course of a working day, which causes general discomfort and pain, especially in older people. This condition is often treated with medication rather than movement. An alternative is wearing compression stockings or bandages, which many sufferers find uncomfortable due to the skin irritation caused by constant skin contact of the bandage under pressure.
  • the device according to the invention can be used because of its simple handling.
  • the cuff is placed on the calf area and the intermittent compression is triggered by switching on the pump or its control.
  • Intermittent compression not only stimulates the return transport of venous blood, but also the return transport of lymphatic fluid, the reabsorption of ultrafiltrate into the venous system and the passage of protein-rich liquids through tissue splitting in edema, which leads to a general detoxification of the organism and swelling is reduced.
  • Another preferred application is the prophylaxis of venous thrombosis. It is known that when there is a lack of movement, for example when sitting or postoperatively when the patient is in bed, blood coagulation occurs spontaneously or partly spontaneously, particularly in the calves or lower extremities. Blood clots block the blood vessels and, if they are carried into the lung area, can lead to life-threatening embolisms. Whenever venous blood is not being removed quickly enough but is jammed, the likelihood of blood coagulation is greater due to the changed blood coagulation behavior.
  • heparin is usually administered at regular intervals for anticoagulation, especially after operations, and the wearing of compression stockings is prescribed. Due to the very simple, inexpensive and handy construction of the device according to the invention, the intermittent compression is a real addition or even an alternative to these measures.
  • the re-stimulation of the venous return of blood results in improved blood coagulation behavior and smaller blood clots are dissolved again (fibrinolysis).

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  • Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Pain & Pain Management (AREA)
  • Physical Education & Sports Medicine (AREA)
  • Rehabilitation Therapy (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Epidemiology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Massaging Devices (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
  • Pharmaceuticals Containing Other Organic And Inorganic Compounds (AREA)
  • Control Of Multiple Motors (AREA)

Claims (10)

  1. Mécanisme destiné à être utilisé en tant que mécanisme, approprié pour une mise en oeuvre mobile, transportable sans difficulté, pour la compression intermittente d'extrémités humaines, pour soutenir un reflux de liquide corporel en direction du coeur, caractérisé par la combinaison des caractéristiques suivantes :
    a) le mécanisme comprend une manchette (2), à appuyer sur une extrémité
    b) un générateur de pression miniature (1) pour une alimentation en pression intermittente de la manchette (2) avec une pression maximale, mesurée par rapport à la pression atmosphérique, entre 20 mm Hg et 100 mm Hg, qui est appliquée directement sur la manchette (2), moyennant quoi
    c) la manchette (2) ne présente, dans la direction du reflux, qu'une largeur (B) d'au plus 25 cm et
    d) est constituée en tant que système à chambre unique,
    e) et une unité de commande (5), qui met en et hors circuit le générateur de pression (1) et, de ce fait, alimente en pression la manchette (2) avec une pression d'une portée prédéterminée ou pouvant être prédéterminée et une fréquence de répétition prédéterminée ou pouvant être prédéterminée.
  2. Mécanisme selon la revendication 1, caractérisé en ce que la manchette (2) correspond à une manchette, utilisée pour les mesures de pression sanguine.
  3. Mécanisme selon l'une des revendications précédentes, caractérisé en ce que le générateur de pression (1) est une pompe à rouleaux.
  4. Mécanisme selon l'une des revendications précédentes, caractérisé par un dispositif de commande de pression, qui, en cas de dépassement d'une surpression prédéterminée dans une chambre de manchette, relie cette chambre de manchette à l'air ambiant.
  5. Mécanisme selon la revendication 4, caractérisé en ce que le dispositif de commande de pression comprend une soupape de décharge (21,22), qui forme une décharge de surpression pour la manchette (2), qui est ouverte en permanence, sauf quand le générateur de pression (1) alimente la manchette (2) en pression.
  6. Mécanisme selon l'une des revendications précédentes, caractérisé en ce que le dispositif de commande de pression présente un restricteur (6b) dans une jonction (6) entre le générateur de pression (1) et la manchette (2) et une soupape de décharge (21, 22) avec un organe d'arrêt (22), qui, dans une première position, libère une décharge (21) dans l'air ambiant et, dans une deuxième position, la bloque, l'organe d'arrêt (22) occupant ces positions en fonction d'une différence de pression entre une admission et une évacuation du restricteur (6b).
  7. Mécanisme selon l'une des revendications précédentes, caractérisé en ce que l'unité de commande (5) est conçue pour modifier l'amplitude de la pression et / ou la fréquence de répétition.
  8. Mécanisme selon l'une des revendications précédentes, caractérisé en ce que la manchette (2) est alimentée en pression entre une et dix fois par minute.
  9. Mécanisme selon l'une des revendications précédentes, caractérisé en ce que la manchette (2) est alimentée en pression entre une et quinze fois par cinq minutes.
  10. Mécanisme selon l'une des revendications précédentes, caractérisé en ce que le générateur de pression (1) peut être désaccouplé de la manchette (2); de préférence au moyen d'un raccord à fermeture rapide.
EP99938212A 1998-06-26 1999-06-25 Dispositif de compression intermittente Expired - Lifetime EP1089701B1 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
DE19828588A DE19828588C2 (de) 1998-06-26 1998-06-26 Transportable Vorrichtung zur intermittierenden Kompression zur Unterstützung eines Rücktransports von Körperflüssigkeit in Richtung des Herzens, und Verwendung dieser Vorrichtung
DE19828588 1998-06-26
PCT/EP1999/004439 WO2000000153A2 (fr) 1998-06-26 1999-06-25 Dispositif de compression intermittente

Publications (2)

Publication Number Publication Date
EP1089701A2 EP1089701A2 (fr) 2001-04-11
EP1089701B1 true EP1089701B1 (fr) 2004-12-29

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EP99938212A Expired - Lifetime EP1089701B1 (fr) 1998-06-26 1999-06-25 Dispositif de compression intermittente

Country Status (7)

Country Link
US (1) US6905456B1 (fr)
EP (1) EP1089701B1 (fr)
JP (1) JP2003521268A (fr)
AT (1) ATE285740T1 (fr)
AU (1) AU5280199A (fr)
DE (2) DE19828588C2 (fr)
WO (1) WO2000000153A2 (fr)

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DE102006033033B4 (de) * 2006-07-14 2010-01-28 W. Krömker GmbH Kompressionsverband
JP2008246196A (ja) * 2007-03-22 2008-10-16 Dynatherm Medical Inc 血液循環を調整するための方法及び装置
US8388557B2 (en) 2007-06-20 2013-03-05 Remo Moomiaie-Qajar Portable compression device
US8251932B2 (en) * 2008-10-20 2012-08-28 Breg, Inc. Orthopedic walker boot having an inflatable bladder
WO2011005538A2 (fr) * 2009-06-23 2011-01-13 Boris Leschinsky Procédés et dispositifs pour préconditionnement ischémique à distance et contrôle presque continu de la pression sanguine à distance
US8517729B2 (en) * 2010-03-04 2013-08-27 The University of Western Ontario and Trudell Medical International Oral mouthpiece and method for the use thereof
US8506507B2 (en) * 2010-03-09 2013-08-13 Covidien Lp Venous augmentation system
TW201143740A (en) * 2010-06-03 2011-12-16 Hon Hai Prec Ind Co Ltd Spinal adjustment device
ES2616808T3 (es) 2010-10-04 2017-06-14 Chu Sainte-Justine Métodos de base biomecánica de diagnóstico de escoliosis
WO2012134939A2 (fr) * 2011-03-25 2012-10-04 Logan Kerry Modèle amélioré de dispositif pour compression pneumatique intermittente
US8764789B2 (en) 2011-04-15 2014-07-01 CellAegis Devices Inc. System for performing remote ischemic conditioning
US20140094727A1 (en) * 2012-09-28 2014-04-03 Covidien Lp Compression device pumping
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US11839588B2 (en) * 2014-07-17 2023-12-12 Gnotrix, Llc Systems and methods for multiple pulses for treatment of vascular conditions
US10166166B1 (en) * 2015-08-11 2019-01-01 Trevor James Theriot Apparatus for applying periodic pressure to the limb of a patient and method of use
US10166164B2 (en) 2016-04-27 2019-01-01 Radial Medical, Inc. Adaptive compression therapy systems and methods
US10939920B2 (en) * 2018-01-10 2021-03-09 Tej M. Singh Hemodialysis vein preparation method

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Also Published As

Publication number Publication date
AU5280199A (en) 2000-01-17
ATE285740T1 (de) 2005-01-15
WO2000000153A2 (fr) 2000-01-06
US6905456B1 (en) 2005-06-14
DE19828588A1 (de) 1999-12-30
DE59911372D1 (de) 2005-02-03
EP1089701A2 (fr) 2001-04-11
JP2003521268A (ja) 2003-07-15
DE19828588C2 (de) 2002-11-14
WO2000000153A3 (fr) 2000-02-10

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