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WO1996006572A1 - Dispositif pour stopper le saignement de tissus vivants chez l'homme et chez les animaux - Google Patents

Dispositif pour stopper le saignement de tissus vivants chez l'homme et chez les animaux Download PDF

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Publication number
WO1996006572A1
WO1996006572A1 PCT/SE1994/000790 SE9400790W WO9606572A1 WO 1996006572 A1 WO1996006572 A1 WO 1996006572A1 SE 9400790 W SE9400790 W SE 9400790W WO 9606572 A1 WO9606572 A1 WO 9606572A1
Authority
WO
WIPO (PCT)
Prior art keywords
plasma
tissue
section
sections
channel
Prior art date
Application number
PCT/SE1994/000790
Other languages
English (en)
Inventor
Nikolai Suslov
Original Assignee
Nikval International 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
Priority to SE9301850A priority Critical patent/SE503334C2/sv
Priority to ES94929701T priority patent/ES2207640T3/es
Priority to DK94929701T priority patent/DK0784452T3/da
Priority to AU78657/94A priority patent/AU7865794A/en
Priority to EP94929701A priority patent/EP0784452B1/fr
Priority to JP50865196A priority patent/JP3565561B2/ja
Application filed by Nikval International Ab filed Critical Nikval International Ab
Priority to PCT/SE1994/000790 priority patent/WO1996006572A1/fr
Priority to CA002198000A priority patent/CA2198000C/fr
Priority to US08/809,203 priority patent/US5843079A/en
Priority to AT94929701T priority patent/ATE252348T1/de
Priority to DE69433269T priority patent/DE69433269T2/de
Publication of WO1996006572A1 publication Critical patent/WO1996006572A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/042—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating using additional gas becoming plasma
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/1206—Generators therefor
    • A61B2018/1213—Generators therefor creating an arc

Definitions

  • the subject invention concerns a device to stop bleeding in live human and animal tissue and to form a crust by means of a plasma jet.
  • the invention relates to plasma surgery and more particularly to a new and improved plasma surgical technique of achieving coagulation or a hemostatic effect, i.e. desiccation and coagulation by weak supply of plasma jet power to a layer of tissue and intense supply of jet power to the fluid component of the biological tissue.
  • the purpose of the invention resides in plasma dynamic desic ⁇ cation of a surgical site and in the creation in said site of an area of thermal necrosis at a rate highly exceeding the rate of medium or in ⁇ tense bleeding with the aid of direct application of a plasma jet having definite thermo-dynamic characteristics.
  • Plasma flow, laser irradiation and electrosurgery are methods used in surgery for clean-cutting purposes, for combined cutting and hemostasis effect as well as for obtaining hemostasis of a surgical wound.
  • thermochemical The dominant reactions induced by intense energy application on tissue are thermochemical in nature as a result of the energy absorption by the biological object. The major part of the energy is converted into heat.
  • ATC area of thermal changes
  • heat is in this case conducted to the boundary of vaporization of the liquid component by means of thermal conductivity. Because during the desiccation of tissue its thermal conductivity is reduced by 4-6 times compared with undesiccated tissue and by 0.62 W/m . °C, the rate of the displacement of the va ⁇ porization boundary with respect to the liquid component diminishes as well, which means that the rate of the ATC creation goes down considerably.
  • the use of this method allows the spongy necrosis layer to be obtained only during weak and rather moderate bleeding. This may be understood by the following example.
  • the thermal flow at the boundary of vaporization of the liquid component in the tissue must exceed 4.6 x 10 6 W/m 2 .
  • the quantity of thermal flow at the boundary of liquid vaporiza ⁇ tion of the liquid component does not exceed 4 x 10 5 W/m 2 .
  • energy is supplied to a tissue and allow to penetrate into it.
  • a YAG (Nd-YAG) laser beam in the visible and the near-infra ⁇ red region is used as well as electrosurgical application.
  • the energy is absorbed into the tissue to a depth of 1.0 mm.
  • the amount of thermal energy penetrating into the unit volume of tissue must slightly exceed the energy required to vaporize the blood flow in the tissue and the application must be terminated at the moment of achieving desiccation.
  • the energy supply to the tissue is effected by application of high-frequency current to the tissue.
  • desic- cation As soon as desic- cation is achieved, its impedence increases considerably, resulting in termination of the application and the achievement of a desiccated layer.
  • this method involves feedback during the applica ⁇ tion because the energy supply stops at the moment of tissue surface desiccation, i.e. after the final creation of the spongy necrosis layer. This deminishes the generally harmful effect of the method and provi ⁇ des an opportunity to chose determined regimes with guaranteed power amounts and hence with guaranteed achievement of arresting intensive bleeding.
  • the main disadvantages of electrosurgical application on biolo ⁇ gical tissue are the following. In order to stop intensive bleeding it is necessary to increase the amount of energy of the application, which is carried out at the expense of the regime of the microarc generation between the tissue and the surgical instrument.
  • the emission of ener- gy in biological tissue involves passing current through a patient, which may limit its usage (for instance in the case of heart diseases). This method does not allow precise incision to be made in tissue in contrast to the characteristics of the laser beam method.
  • Fig. 1 is a cross-sectional view through a wound in tissue that has been treated by means of the device in accordance with the in ⁇ vention
  • Fig. 2 is a corresponding cross-sectional view through tissue treated by means of an electrosurgical method
  • Figs. 3a and b are corresponding sectional views schematically illustrating the inter-active flows to and away from a tissue
  • Figs. 4 and 5 shows coordinate systems with curves represen ⁇ ting measured values of thermal energy as a function of plasma jet temperatures
  • Fig. 6 is longitudinal sectional view through a plasma nozzle in accordance with one embodiment of the invention wherein an inert gas is used,
  • Fig. 6a is a cross-sectional view along line A-A in Fig. 6,
  • Figs. 7 and 7a are corresponding sectional views but show a different embodiment of the plasma nozzle wherein the used gas is air and
  • Figs. 8 and 8a are corresponding sectional views of a third em ⁇ bodiment of the plasma nozzle using water vapor.
  • Fig. 1 is sectional view through a treated wound in a tissue.
  • Numeral reference 1 designates a spongy desiccated layer showing locally dead cells (necrosis). This layer 1 is covered by a carbonized layer 2. Owing to heat transfer a compact necrosis layer 3 has formed underneath the spongy desiccated layer 1. The necrosis layer is for ⁇ med between the spongy layer 1 and the unaffected, live tissue 4.
  • Fig. 2 shows a wound treated with the aid of electrosurgical technique.
  • the spongy layer 1 is characterized by an ex ⁇ ternal, essentially uniform-depth supporting tissue (reticulum) having holes 5 created by means of a light arc.
  • the holes are essentially of identical cross-sectional area and are essentially evenly distributed across the eschar surface.
  • the tissue intermediate adjacent holes 5 confers pliability to the eschar, preventing cracking.
  • generally uniform-depth thermally desiccated layer 3 separates the arc hole re ⁇ ticulum from the unaffected tissue.
  • the high porosity of the necrosis layer (as will be shown below it amounts to approximately the percentage of fluid component in the tissue -75-85%) makes it possible to use the essentially novel method of plasma flow to obtain this layer under extensive bleeding condi ⁇ tions.
  • the presence of various forms of energy resources is typical of plasma jet.
  • the plasma flow energy is concentrated as a form of plas- ma enthalpi, a dynamic component of jet energy and broadband emission of ionized gas.
  • the cross-sectional area of the plasma jet and its tem ⁇ perature it becomes possible to control the dynamic pressure of the plasma flow. Consequently, it becomes possible to establish inter- action between the plasma jet and the spongy necrosis layer when the plasma jet penetrates this layer completely or partly.
  • the plasma jet is partly cooled while heating the spongy necrosis layer and the remaining part of the jet energy is absorbed at the boundary of the vaporization of the tissue fluid component.
  • the filtration of the cooled plasma-generating gas and of the vapour flow takes place through the low pressure area of the plasma jet.
  • the maximum cross-section of a plasma jet that realizes penetration of plasma flow in the spongy necrosis layer to a depth of about 0.25 mm equals 3.5 mm in lungs, 3.0 mm in the spleen, 2.5 mm in the liver and 1.5 mm in kidneys.
  • Figs. 4 and 5 The results of these investigations are shown in Figs. 4 and 5.
  • the black dots correspond to the values of the thermal power and plasma jet temperatures that provide reliable arrest of intensive bleeding.
  • Lines I, II, III illustrate the parameters of the plasma jet bo ⁇ undaries beyond which it was not possible to stop bleeding.
  • thermo-physical characteristics of the tissue upon phase-structural changes and the formation of ATC - distinction between temperatures of vaporization of the liquid com ⁇ ponent of the tissue and of the sublimation of the charring spongy layer
  • Boundary line I defines the condition of gasodynamic penet ⁇ ration of the plasma flow into a porous dessicated tissue layer, to a depth of 0.2-0.25 mm, i.e. exceeding by 3-5 times the a characteristic cross-section of the pores d.
  • the position of the boundary I is deter ⁇ mined by tissue species and depends on the cross-sectional area of the plasma jet.
  • Boundary line II defines the condition of vaporization of the liquid component of the tissue at a rate exceeding the rate of bleeding.
  • the position of boundary II is determined by the extent of cooling of the plasma jet in the bulk of the spongy necrosis layer and is defined by the parameter ⁇ r .
  • Boundary line III defines the condition of intensive sublima ⁇ tion of a carbonized spongy layer when the boundary of tissue subli ⁇ mation coincides with the boundary of the fluid component. Besides the limitations mentioned it is necessary to also take into account that the very considerable volume increase of the plasma-generating gas consumption may be the cause of the generation of gaseous em ⁇ bolism. Investigations show that in order to exclude gaseous embo ⁇ lism appearance the value of argan and air consumption must not exceed 2.0 1/min.
  • the gas providing the widest range of change of the plasma pa ⁇ rameters and able to arrest heavy bleeding is argon.
  • the use of air as the plasma generating gas could also make it possible to stop intensi- ve bleeding but within a much narrower range of plasma parameters compared with argon. It should be noted that in order to generate plasma flows having the above-mentioned parameters some limita- tions of the plasma surgical instrument must be respected.
  • surgical microplasmatrons must generate plasma flows having an average mass temperature valid for the given type of gas (argon or air) of a necessarily comparatively high value (argon 7500 - 10 500° K, air 4500 - 5000° K) and that must change only insignificantly during fluctuations of consumption of the plasma-generating gas (between the limits 1.0-2.0 1/min). Furthermore, the above parameters of plas ⁇ ma flow must be achieved with limitation of the value of the discharge current at a level near 30 A, excluding erosion of the electrodes of the microplasmatron .
  • the plasma- surgical instrument In order to obtain a guaranteed hemostatic effect in the wound surface during a significant change of the bleeding intensity it is ne ⁇ cessary that the plasma- surgical instrument generates a plasma jet at a stable and comparatively high level of its temperature.
  • the jet tem- perature must not change significantly during the regulation of the consumption of the plasma-generating gas.
  • This cross-section of the electrical arc results in a high value of the electrical field strength in the channel and the length of the chan- nel that is necessary to heat the argon at the consumption rate of 2.0 1/min is insufficient to provide the electric discharge-distance strength.
  • a voltage drop in the plasma of the electric arc increases above 15- 16 V (total value of voltage step input) and in con ⁇ sequence thereof instead of one long arc two sequential arcs appear, burning at a lower voltage and not providing gas heating to a high temperature.
  • this channel is designed as electrically isolated sections. Its number must not be less than three.
  • the highest electrical field strength is generated by the initial field of the electric arc at the cathode where a cooled gas enters into the arc.
  • the length of the channel sections must be increased at a distance from the cathode since the field strength decreases.
  • the sections are interconnected via non-electric- ally conductively gaskets.
  • the first channel section is connected to the positive pole of a pulse periodic energy accumulator and to a high- voltage spark gap (triggering system of a surgical microplasmatron) .
  • the last section is connected to the positive pole of a main power source in the surgical microplasmatron.
  • a suitable length of this section is two to three times the diameter of channel d. All chan ⁇ nel sections with the exception of the last one have the same cross- sectional dimensions.
  • the last section should, for the purpose of dis- secting tissues in optimal modes of operations, have a channel width of 0.4-0.6 mm. Its design when employed for this purpose does not depend on the kind of plasma-generating gas used.
  • the cross- sectional size of the last channel section does, however, depend on both tissue species and type of plasma- generating gas.
  • the cross-sectional dimensions of the last channel sections should be 2.5 mm and in the case of kid- neys 1.5 mm.
  • a basic embodiment of a plasma surgical unit consisting of an electrically conductive body 6 similar to a pencil with a tip 7 for forming a plasma jet having the required cross- section and connected to a positive pole of a gas power source having a positive potential.
  • the body 6 comprises a cylindrical channel to heating the plasma-generating gas and it is formed from channel sec ⁇ tions 8, 9, 10 which are electrically isolated from each other and which are connected to the body 6 through an electrically isolated concentric bush 1 1 having channels 12 for conveyance of cooling fluid to and from the gas heat-ing channel.
  • the sections 8, 9, 10 are inter ⁇ connected by means of non-electrically conductive sleeves 22.
  • the last section 10 which is designed to form the plasma jet, is connected with the tip 7 and has a channel cross-section df to stop bleedings from large surgical wounds.
  • the cross-section depends on the kind of plasma-generating gas and the species of the biological tissue.
  • the channel of section 10 is constructed as two co-axial cylindrical holes 17, 18 (see Fig.
  • the first section 8 is configured as a hollow cylindrical electrode which is connected with the body 6 via the electrically isolated bush 1 1 and with the cathode 13, 14 via the electrically isolated sealing bush 15.
  • the sections are mutually interconnected via electrically in ⁇ sulated gaskets 22.
  • the cathode consists of an electrically conductive tube 14 on one end of which the electrode 13 from a high-melting metal is fixed, providing the required level of current for thermal-electronic emission within the working range of discharged currents.
  • the opposite end of the tube serves as a connection to the gas supply unit and is connec- ted with the negative poles of the basic energy source and of the trig ⁇ ger system of the microplasmatron.
  • the electrically conductive tube 14 is formed with holes 16 for input and uniform distribution of the plasma-generating gas to the discharge chamber of the micro ⁇ plasmatron.
  • the electrode of the cathode 13 is made from wolfram or its alloys.
  • the electrode of the cathode 13 is made from zirconium or hafnium (Figs. 7, 8).
  • the second last and the last sections 9 and 10 are formed at the beginning and the end, respectively, with tangentially positioned channels 19 (see Fig. 8) which are connected to the channel heating the plasma-generating gas and having the volume separated from the cooling water by means of inserts 20 formed with pores positioned in ⁇ side a heat insulated cylindrical sleeve 21.
  • the porous inserts 20 cover at least half of the external surface of the second last and the last sections 9 and 10.
  • the water-filled cavity is connected to a system regulating the water pressure in order to control the quantity of steam consumption.
  • the discharge current provides the required tempera ⁇ ture of the plasma flows and the size of the steam consumption is between 3.0 and 8.0 A.
  • the eschar resulting from the use of the device proposed in accordance with the subject invention has a well defined spongy necrosis layer having a thickness of 0.15-0.25 mm, which corresponds to between 3 and 5 characteristic cross- sections of pores therein.
  • the porous layer in accordance with the invention has a well defined boundary towards the subjacent tissue, which indicates the highly restricted heat penetration into the tissue and the localisation in this area of the boundary of vaporization of the liquid component of the tissue.
  • SNL spongy necrosis layer
  • the pore size upon plasma exposure is 1.5 times less that upon laser exposure and the thickness of tissue intermediate the pores is 1.3 times larger. This indicates that the permiability of a spongy des- sicated layer is approximately similar to that of a dessicated tissue obtained by means of methods involving slow heating at a tempera ⁇ ture which only slightly exceeds that of vaporization of the tissue liq ⁇ uid component of the tissue.

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  • Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Molecular Biology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Plasma & Fusion (AREA)
  • Physics & Mathematics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Otolaryngology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Surgical Instruments (AREA)
  • Plasma Technology (AREA)
  • Materials For Medical Uses (AREA)

Abstract

L'invention concerne un dispositif conçu pour améliorer la coagulation de tissus vivants saignant modérément ou abondamment chez l'homme et chez les animaux et pour former une croûte du type escarre au moyen d'un jet de plasma. Ce dispositif comporte un moyen de génération de plasma consistant en un corps électroconducteur (6) qui est connecté à un pôle positif d'une source d'énergie de base à potentiel positif. Le corps (6) est constitué d'un canal cylindrique (17) conçu pour chauffer le gaz générant le plasma. La canal (17) est formé à partir de plusieurs sections (8, 9, 10) qui sont isolées électriquement les unes des autres, chacune étant connectée audit corps par des douilles (22) concentriques avec les sections (8, 9, 10) et isolées électriquement. Ces douilles (22) sont dotées de canaux (19) permettant la circulation du liquide de refroidissement en direction du canal chauffant le gaz (17) et en provenance de celui-ci.
PCT/SE1994/000790 1993-06-01 1994-08-29 Dispositif pour stopper le saignement de tissus vivants chez l'homme et chez les animaux WO1996006572A1 (fr)

Priority Applications (11)

Application Number Priority Date Filing Date Title
SE9301850A SE503334C2 (sv) 1993-06-01 1993-06-01 Anordning för att stoppa en blödning och bilda en sårskorpa medelst en plasmastråle
DK94929701T DK0784452T3 (da) 1994-08-29 1994-08-29 Apparat til at standse blødning i levende humant og animalt væv
AU78657/94A AU7865794A (en) 1993-06-01 1994-08-29 A device to stop bleeding in living human and animal tissue
EP94929701A EP0784452B1 (fr) 1994-08-29 1994-08-29 Dispositif pour stopper le saignement de tissus vivants chez l'homme et chez les animaux
JP50865196A JP3565561B2 (ja) 1994-08-29 1994-08-29 人間および動物の生体組織内の出血を停止する装置
ES94929701T ES2207640T3 (es) 1994-08-29 1994-08-29 Dispositivo para detener las hemorragias de los tejidos vivos de los seres humanos y los animales.
PCT/SE1994/000790 WO1996006572A1 (fr) 1993-06-01 1994-08-29 Dispositif pour stopper le saignement de tissus vivants chez l'homme et chez les animaux
CA002198000A CA2198000C (fr) 1993-06-01 1994-08-29 Dispositif pour arreter le saignement de tissus d'humains ou d'animaux vivants
US08/809,203 US5843079A (en) 1994-08-29 1994-08-29 Device to stop bleeding in living human and animal tissue
AT94929701T ATE252348T1 (de) 1994-08-29 1994-08-29 Blutstillungsvorrichtung für lebendes menschliches und tierisches gewebe
DE69433269T DE69433269T2 (de) 1994-08-29 1994-08-29 Blutstillungsvorrichtung für lebendes menschliches und tierisches gewebe

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
SE9301850A SE503334C2 (sv) 1993-06-01 1993-06-01 Anordning för att stoppa en blödning och bilda en sårskorpa medelst en plasmastråle
PCT/SE1994/000790 WO1996006572A1 (fr) 1993-06-01 1994-08-29 Dispositif pour stopper le saignement de tissus vivants chez l'homme et chez les animaux

Publications (1)

Publication Number Publication Date
WO1996006572A1 true WO1996006572A1 (fr) 1996-03-07

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PCT/SE1994/000790 WO1996006572A1 (fr) 1993-06-01 1994-08-29 Dispositif pour stopper le saignement de tissus vivants chez l'homme et chez les animaux

Country Status (4)

Country Link
AU (1) AU7865794A (fr)
CA (1) CA2198000C (fr)
SE (1) SE503334C2 (fr)
WO (1) WO1996006572A1 (fr)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2004030551A1 (fr) * 2002-10-04 2004-04-15 Plasma Surgical Investments Limited Dispositif chirurgical au plasma
EP1089668B1 (fr) * 1998-06-24 2005-05-25 Plasma Surgical Investments Limited Couteau au plasma
US7589473B2 (en) 2007-08-06 2009-09-15 Plasma Surgical Investments, Ltd. Pulsed plasma device and method for generating pulsed plasma
JP2010536123A (ja) * 2007-08-06 2010-11-25 プラズマ スルギカル インベストメントス リミテッド パルスプラズマを生成するパルスプラズマ装置および方法
WO2011091855A1 (fr) * 2010-01-29 2011-08-04 Plasma Surgical Investments Limited Procédés destinés à sceller des récipients en utilisant un plasma
WO2012005132A1 (fr) 2010-07-07 2012-01-12 独立行政法人産業技術総合研究所 Dispositif de traitement par irradiation plasma
US9089319B2 (en) 2010-07-22 2015-07-28 Plasma Surgical Investments Limited Volumetrically oscillating plasma flows
US9913358B2 (en) 2005-07-08 2018-03-06 Plasma Surgical Investments Limited Plasma-generating device, plasma surgical device and use of a plasma surgical device
US11882643B2 (en) 2020-08-28 2024-01-23 Plasma Surgical, Inc. Systems, methods, and devices for generating predominantly radially expanded plasma flow
CN117860369A (zh) * 2024-01-19 2024-04-12 遵义医科大学珠海校区 一种用于经皮肾镜的止血操作器

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3991764A (en) * 1973-11-28 1976-11-16 Purdue Research Foundation Plasma arc scalpel
US4788408A (en) * 1987-05-08 1988-11-29 The Perkin-Elmer Corporation Arc device with adjustable cathode
US4855563A (en) * 1986-08-11 1989-08-08 Beresnev Alexei S Device for plasma-arc cutting of biological tissues
WO1992019166A1 (fr) * 1991-04-15 1992-11-12 Nauchno-Issledovatelsky Institut Energeticheskogo Mashinostroenia Moskovskogo Gosudarstvennogo Tekhnicheskogo Universiteta Imeni N.E.Baumana Dispositif de traitement chirurgical au plasma de tissus biologiques

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3991764A (en) * 1973-11-28 1976-11-16 Purdue Research Foundation Plasma arc scalpel
US4855563A (en) * 1986-08-11 1989-08-08 Beresnev Alexei S Device for plasma-arc cutting of biological tissues
US4788408A (en) * 1987-05-08 1988-11-29 The Perkin-Elmer Corporation Arc device with adjustable cathode
WO1992019166A1 (fr) * 1991-04-15 1992-11-12 Nauchno-Issledovatelsky Institut Energeticheskogo Mashinostroenia Moskovskogo Gosudarstvennogo Tekhnicheskogo Universiteta Imeni N.E.Baumana Dispositif de traitement chirurgical au plasma de tissus biologiques

Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1089668B1 (fr) * 1998-06-24 2005-05-25 Plasma Surgical Investments Limited Couteau au plasma
US7361175B2 (en) 2002-10-04 2008-04-22 Plasma Surgical Investments Limited Plasma surgical device
CN100408000C (zh) * 2002-10-04 2008-08-06 普拉斯马外科投资有限公司 等离子体手术设备
WO2004030551A1 (fr) * 2002-10-04 2004-04-15 Plasma Surgical Investments Limited Dispositif chirurgical au plasma
US12075552B2 (en) 2005-07-08 2024-08-27 Plasma Surgical, Inc. Plasma-generating device, plasma surgical device and use of a plasma surgical device
US9913358B2 (en) 2005-07-08 2018-03-06 Plasma Surgical Investments Limited Plasma-generating device, plasma surgical device and use of a plasma surgical device
US10201067B2 (en) 2005-07-08 2019-02-05 Plasma Surgical Investments Limited Plasma-generating device, plasma surgical device and use of a plasma surgical device
US7589473B2 (en) 2007-08-06 2009-09-15 Plasma Surgical Investments, Ltd. Pulsed plasma device and method for generating pulsed plasma
JP2010536123A (ja) * 2007-08-06 2010-11-25 プラズマ スルギカル インベストメントス リミテッド パルスプラズマを生成するパルスプラズマ装置および方法
WO2011091855A1 (fr) * 2010-01-29 2011-08-04 Plasma Surgical Investments Limited Procédés destinés à sceller des récipients en utilisant un plasma
WO2012005132A1 (fr) 2010-07-07 2012-01-12 独立行政法人産業技術総合研究所 Dispositif de traitement par irradiation plasma
US9089319B2 (en) 2010-07-22 2015-07-28 Plasma Surgical Investments Limited Volumetrically oscillating plasma flows
US10492845B2 (en) 2010-07-22 2019-12-03 Plasma Surgical Investments Limited Volumetrically oscillating plasma flows
US10631911B2 (en) 2010-07-22 2020-04-28 Plasma Surgical Investments Limited Volumetrically oscillating plasma flows
US12023081B2 (en) 2010-07-22 2024-07-02 Plasma Surgical, Inc. Volumetrically oscillating plasma flows
US10463418B2 (en) 2010-07-22 2019-11-05 Plasma Surgical Investments Limited Volumetrically oscillating plasma flows
US11882643B2 (en) 2020-08-28 2024-01-23 Plasma Surgical, Inc. Systems, methods, and devices for generating predominantly radially expanded plasma flow
US12058801B2 (en) 2020-08-28 2024-08-06 Plasma Surgical, Inc. Systems, methods, and devices for generating predominantly radially expanded plasma flow
CN117860369A (zh) * 2024-01-19 2024-04-12 遵义医科大学珠海校区 一种用于经皮肾镜的止血操作器

Also Published As

Publication number Publication date
SE503334C2 (sv) 1996-05-28
CA2198000A1 (fr) 1996-03-07
SE9301850D0 (sv) 1993-06-01
SE9301850L (sv) 1994-12-02
AU7865794A (en) 1996-03-22
CA2198000C (fr) 2006-08-22

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