GB2060397A - Non-adherent surgical instrument and method - Google Patents
Non-adherent surgical instrument and method Download PDFInfo
- Publication number
- GB2060397A GB2060397A GB8028064A GB8028064A GB2060397A GB 2060397 A GB2060397 A GB 2060397A GB 8028064 A GB8028064 A GB 8028064A GB 8028064 A GB8028064 A GB 8028064A GB 2060397 A GB2060397 A GB 2060397A
- Authority
- GB
- United Kingdom
- Prior art keywords
- tissue
- surgical apparatus
- adherent coating
- elevated temperature
- hemostasis
- 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.)
- Granted
Links
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
- A61B18/08—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by means of electrically-heated probes
- A61B18/082—Probes or electrodes therefor
-
- 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
- A61B18/08—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by means of electrically-heated probes
- A61B18/082—Probes or electrodes therefor
- A61B18/085—Forceps, scissors
-
- 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
- A61B2018/00053—Mechanical features of the instrument of device
- A61B2018/00107—Coatings on the energy applicator
-
- 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
- A61B2018/00964—Features of probes
- A61B2018/0097—Cleaning probe surfaces
Abstract
Method and means are disclosed for preventing tissue from adhering to surgical apparatus (e.g. a heated surgical scalpel) while operating at tissue temperatures (usually 100-500 DEG C) at which haemostasis with minimal tissue damage occurs, and include interposing between the surgical apparatus 11 and the tissue 13 being heated thereby a non-adherent coating 12 which has specific parameters including thermal impedance, thickness and thermal drop thereacross. The coating 12 may be of fluorocarbon polymers, silicones, metallic fluorides or organic phosphates, or may be a sacrificial solid or liquid layer of waxes, greases, oils or other fluorinated polymers or silicones. <IMAGE>
Description
SPECIFICATION
Non-adherent surgical instrument and method
This invention is concerned with improvements in
or relating to surgical instruments and with their
method of use.
Surgical devices which heat tissue to provide
hemostasis are described in the literature (see, for example, U S Patents RE 29,088,4,091,813 and 4,185,632). The adherence of tissue to such surgical
devices severely limits their usefulness because the
resulting avulsion of tissue causes undesirable tissue damage and bleeding. Also, the adherence of tissue to such surgical devices limits the surgeon 5 control of the device, and the build-up of adherent tissue material causes apparent dullness of the device. Additionally, the build-up of adherent tissue material on heater-type surgical devices introduces a high thermal impedance between the heater and the tissue being cut that prevents heating of the tissues to the desired temperature.These problems of tissue adhering to the surgical device are especially severe for tissue temperatures within the range from about 1000C to about 500"C.
The applicant has discovered that the tissue temperature for the optimum condition of hemostasis with minimal tissue damage varies with the type of tissue being cut and may be as low as about 1300C (on the soft palate of the mouth) and as high as about 45000 to 5000C (on highly vascularized tissue), above which tissue adherence usually does not occur.
The present invention provides surgical apparatus for non-adherently contacting tissue to heat the tissue in contact therewith to an elevated temperature at which hemostasis with minimal tissue damage occurs, comprising: heating means operable at an elevated temperature for heating the tissue; and non-adherent coating means disposed to be intermediate the heating means and the tissue being heated thereby; said non-adherent coating means having a thermal impedance that is not substantially greater than C . cm2 watt The present invention further provides surgical apparatus for non-adherently contacting tissue to heat the tissue in contact therewith to an elevated temperature at which hemostasis with minimal tissue damage occurs, comprising: heating means operable at an elevated temperature for heating the tissue; and non-adherent coating means disposed to be intermediate the heating means and the tissue being heated thereby; said non-adherent coating means having a thickness that is not substantially greater than .0025 cm.
The present invention further provides surgical apparatus for non-adherently contacting tissue to heat the tissue in contacttherewithto an elevated temperature at which hemostasis with minimal tissue damage occurs, comprising: heating means operable at an elevated temperature for heating the tissue; and non-adherent coating means disposed to be intermediate the heating means and the tissue being heated thereby; said non-adherent coating means having a thermal drop thereacross while in contact with the tissue that is not substantially greates than 50 C for tissue temperatures within the range from about 10000 to about 50000.
The present invention further provides surgical apparatus for non-adherently contacting tissue to heat the tissue in contact therewith to an elevated temperature at which hemostasis with minimal tissue damage occurs, comprising: heating means operable at an elevated temperature for heating the tissue; and non-adherent coating means disposed to be intermediate the heating means and the tissue being heated thereby; said non-adherent coating means having a maximum allowed thickness, t, in centimeters as given by the relationship: 50 ~ k
(0/A)
(QIA) where k is thermal conductivity of the non-adherent coating in watts/cm0C, and O/A is the heat flux in watts/cm2.
In apparatus as set out forth in anyone of the last four immediately preceding paragraphs, the nonadherent coating means may include a composition selected from fluorocarbon polymers, silicone polymers, organic phosphates or metallic fluorides.
The present invention further provides a method of preventing adherence of surgical apparatus to tissue at an elevated temperature at which hemostasis with minimal tissue damage occurs, the method comprising the steps of: transferring heat to the tissue from the surgical apparatus; and interposing between the tissue and the surgical apparatus a non-adherent coating having a thickness which is not substantially greater than .0025 cm.
The present invention further provides a method of preventing adherence of surgical apparatus to tissue at an elevated temperature at which hemostasis with minimal tissue damage occurs, the method comprising the steps of: transferring heat to the tissue from the surgical apparatus; and interposing between the tissue and the surgical apparatus a non-adherent coating having a maximum allowed thickness, t, in centimeters as given by the relationship: 50 50 k
(QIA) where k is thermal conductivity of the non-adherent coating in watts/cm0C, and Q/A is the heat flux in watts/cm2.
The present invention further provides a method of preventing adherence of surgical apparatus to tissue at an elevated temperature at which hemostasis with minimal tissue damage occurs, the method comprising the steps of: transferring heat to the tissue from the surgical apparatus; and interposing between the tissue and the surgical apparatus a non-adherent coating having athermal impedance which is not substantially greater than C cm2
5.
watt The present invention further provides a method
of preventing adherence of surgical apparatus to tis
sue at an elevated temperature at which hemostasis with minimal tissue damage occurs, the method comprising the steps of: transferring heat to the tissue from the surgical apparatus; and interposing between the tissue and the surgical apparatus a non-adherent coating having a thermal drop thereacross while in contact with tissue that is not substantially greater than 500C for tissue temperatures within the range from about 1 000C to about 500 C.
In accordance with the present invention, the optimum conditions of hemostasis with minimal tissue damage can be attained by operating at tissue temperatures in the range from about 1 000C to about 5000C and by introducing between the surgical device and the contacted tissue a non-adherent coating having specific thermal parameters.
More particularly, in surgical apparatus which operates at elevated temperatures for heating the tissue contacted thereby, the heat transfer from the apparatus to the tissue in regions of the apparatus in contact with tissues may be twenty times greater than the heat transfer from the apparatus to the air in regions of the apparatus that are not in contact with tissue. The heat transfer conditions vary widely as a function of the type of tissue being cut, the desired operating temperature, and the speed at which the device is moved through tissue.
To obtain optimum conditions of hemostasis with minimal tissue damage, the surgical device should rapidly elevate the temperature of the tissue to a preselected narrow range (usually between 1000C and 500 C) and should maintain the tissue temperature within that range as cutting proceeds.
Any accumulation of tissue on that portion of the surgical device that contacts tissue can interpose a thermal impedance between the device and the tissues which may inhibit heat transfer and cause the temperature of the contacted tissue to drop below the value at which the optimum conditions of hemostasis with minimal tissue damage occur.
Therefore, according to the present invention, a non-adherent coating is provided on the tissuecontacting surface of the surgical device which has thermal properties and characteristics within specific limits to assure that the temperature of tissue remains within the optimum rnngefgrwhich hemostasis and minimal tissue damage occur.
There now follows a detailed description which is to be read with reference to the accompanying drawings of several embodiments of the present invention; it is to be clearly understood that these embodiments have been selected for description to illustrate the invention by way of example and not by way of limitation.
In the accompanying drawings:
Figure 1 is a pictorial representation of an electrically-heated scalpel;
Figure 2 is a cross-sectional view of one embodi mentofthe present invention in which a heated surgical scalpel includes a non-adherent coating;
Figure 3 is a cross-sectional view of another
embodiment of the present invention in which a
heated surgical hemostat includes a non-adherent coating;
Figure 4 is a cross-sectional view of another embodiment of the present invention in which a sin to red porous blade structure with interconnecting
passages provides a reservoir of non-adherent material;
Figure 5 is a detailed cross-sectional view of an embodiment of the present invention which illustrates the non-adherent coating on the surgical instrument disposed adjacent to the tissue being cut; and
Figure 6 is a graph which illustrates the parameters of a non-adherent coating according to the present invention.
Referring now to Figure 1, there is shown a surgical scalpel having a blade protion 11 with a cutting edge 10 and an attached handle portion 8 which also carries a conductor of heating power from source 9 to the blade 11 to heat the same, as taught in the prior art. As shown in Figure 2, the surfaces of the blade 11, at least nearthe cutting edge 10, operate at elevated temperatures and contact tissue 13 via a non-adherent coating 12 interposed between the blade 11 and tissue 13. This eliminates the problem of tissue 13 sticking to the surfaces of blade 11 but introduces a thermal impedance between the heated blade 11 and the tissue 13 in contact therewith.
It has been determined that for portions of the blade 11 in contact with tissue, the heatflux 14 normal to or through the non-adherent coating 12 is approximately 10 to 20 times greater than the heat flux therethrough to the air for portions of the blade 11 not in contact with tissue. This produces temperature differences across the non-adherent coating 12.
Thus, while the blade 11 is out of contact with tissue 13, the effective surface temperature of the nonadherent coating 12 is approximately the same as the temperature of the blade 11. However, when the blade 11 and the non-adherent coating 12 contact the tissue 13, the heat flux 14 passing through the thermal impedance presented by the non-adherent coating 12 causes the surface temperature of the non-adherent coating 12 to decrease below the desired temperature at which the optimum condition of hemostasis and minimal tissue damage occur.
The temperature of the surface of the non-adherent coating 12 may be increased to the desired temperature by increasing the temperature of the blade 11 by an amount sufficient to overcome the thermal drop across the coating 12. However, because of the transient conditions associated with the blade 11 being in and out of contact with tissue 13 during a surgical procedure, the surface temperature of the coating 12 may rise excessively while out of contact with tissue to cause deterioration of the coating 12 and undesirable tissue damage upon recontact with tissue 13, as well as falling excessively when coming into contact with tissues to temperatures that are not hemostatic.
In contrast to these transient operating conditions in surgery, conventional cookware with nonadherent coatings do not involve transient opera tion. The heattransfer rate to an item being cooked is generally constant and is established without regard for damage to living tissue. Cookware also can be operated at highertemperaturesto overcome the effects of high thermal impedance associated with thicker non-adherent coatings. However, for reasons stated above, surgical devices cannot be arbitrarily set at a temperature significantly higher than the optimum temperature at which hemostasis with minimal tissue damage occurs. Also the thicknesses of coatings typically used on cookware cannot be used on surgical devices because of the blunting effect and degradation of the cutting action of a blade that would result.
In accordance with the present invention, the non-adherent coating 12 may be formed as a solid layer or as a sacrificial solid layer or as a sacrificial liquid layer. A solid non-adherent layer 12 may be formed on the device 11 including material such as fluorocarbon polymers (exemplified by the fluorinated ethylenepropylene copolymers, polytetrafluoroethylene and polyethylene terephthalate), or silicones and polydimethylsilozanes with active end groups, for example, of hydroxyl, amine, epoxide or thiol attached to the silicone polymer via a nonhydrolyzable Si-C bond, or fluoride-metal composites such as fluoride impregnated composites, or organic phosphates. Alternatively, a sacrificial solid nonadherent coating may be formed using materials such as silicone greases or hydrocarbon, synthetic and natural ester waxes, or sulfide compounds.In addition, a sacrificial solid non-adherent coating may be formed using fluorinated ethylenepropylene copolymers which have been found to be effective in that a coating thus formed "sloughs off" in thin platelets with use to provide the desired nonadherent characteristics which respect to tissue.
With respect to Figure 4, a sacrificial liquid nonadherent coating may be provided by forming a sintered or porous blade structure 11 with substantially continuous passages therethrough which can be impregnated with a material such as silicone oil, for example, of the type based on dimethyl silicone, or ethers such as perfluoropolysynthetic fluids. The porous and impregnated structure according to Figure 4thus establishes and maintains a continuous film of non-adherent material 12 at the surface of the device 11 which is disposed to contact tissue 13.
In accordance with the present invention, the thermal impedance of the non-adherent coating must be sufficiently low to permit transfer of heat 14 from the device 11 to the tissue 13 in contact therewith as illustrated in Figure 5. In particular, the tolerable thermal impedance of a non-adherent coating 12 depends generally upon the level of heat flux required for a particular surgical application. For example, in ophthalmic, neurological and plastic, the dermatological surgery procedures, hemostasis can be accomplished while cutting using heat fluxes well below 50 watts/cm2. However, surgical procedures involving incisions in highly vascular tissues or rapid movement through tissue may require heat fluxes above 50 watts/cm2 to achieve hemostasis while cutting.
As used herein, "thermal impedance" is defined
as follows: T
(0/A) where R refers to the thermal impedance of the
non-adherent coating in units of OC. . cm2
watt
T refers to the temperature difference across the
non-adherent coating from the interface of the
device 11/non-adherent coating 12 to the outer sur
face of the non-adherent coating 12, in units of C, and O/A refers to the heat flux flowing normal to or
through the non-adherent coating, in units of
watts/cm2.
Referring to Figure 5, the maximum allowed
temperature difference T across the non-adherent
coating under maximum heat flux conditions should
not substantially exceed about 5000 in order to
optimize hemostasis while minimizing tissue dam
age and avoiding exposure of the surgical device
and the non-adherent coating to damaging tempera
tures. This tolerable temperature difference thus estab
lished the thermal impedance for the heat flux levels
that will be encountered during use of the surgical
device. The thermal impedances, as defined above,
for non-adherent coatings 12 operating at specified
levels of heat flux are summarized below:
Maximum Allowed
Thermal Impendance, R,
for Temperature
Heat Flux, OIA Difference, T, (wattslcm# of5O0C.
10 5.0
20 2.5
30 1.7
40 1.3
50 1.0
100 0.5 3
These values of thermal impedance forthe non
adherent coating can establish the maximum
allowed thickness for various non-adherent coat
ings. Referring to Figure 5, the allowed thickness of the non-adherent coating 12 in a direction normal to
the heatflux 14 is given bythe relationship: t = R ~ k
where t refers to the maximum allowed non
adherent coating thickness in units of centimeters, R
is the thermal impedance, as defined previously, and k k refers to effective thermal conductivity of the non- adherent coating 12 in unitsofwatts/cm0C.
The graph of Figure 6 illustrates the relationship
between maximum thickness 18 of the non-adherent
coating 12 and heat flux levels corresponding to high (100 watts/cm2 maximum) and low (30 watts/cm2
maximum) heat flux requirements associated with
various surgical procedures. By way of example, cer
tain fluorocarbon materials that have been found
effective as non-adherent coatings exhibit a thermal conductivity of about .0025 watts/cm0C. In accor dance with the above, the thickness of a nonadherent coating of this material should not be greaterthan .0013 cm (0.5 mil) for operation at high heat flux levels.
In the apparatus of Figure 3, a pinch-type instrument 15 (such as a hemostat) may be heated in conventional manner by a source of heating power connected thereto to transfer heat 14 to tissue 16 via the non-adherent coating 12 interposed therebetween.
The maximum allowed thickness of non-adherent coating 12 is determined, as discussed above, with respect to the thermal impedance of the coating material and the operating level of heat flux involved.
Claims (12)
1. Surgical apparatus for non-adherently contacting tissue to heat the tissue in contact therewith to an elevated temperature at which hemostasis with minimal tissue damage occurs comprising:
heating means operable at an elevated temperature for heating the tissue; and
non-adherent coating means disposed to be intermediate the heating means and the tissue being heated thereby; said non-adherent coating means having a thermal impedance that is not substantially greater than 5 . cm2
5
watt
2.Surgical apparatus for non-adherently contacting tissue to heat the tissue in contact therewith to an elevated temperature at which hemostasis with minimal tissue damage occurs, comprising:
heating means operable at an elevated temperature for heating the tissue; and
non-adherent coating means disposed to be intermediate the heating means and the tissue being heated thereby; said non-adherent coating means having a thickness that is not substantially greater than .0025 cm.
3. Surgical apparatus for non-adherently contacting tissue to heat the tissue in contact therewith to an elevated temperature at which hemostasis with minimal tissue damage occurs, comprising:
heating means operable at an elevated temperature for heating the tissue; and
non-adherent coating means disposed to be intermediate the heating means and the tissue being heated thereby; said non-adherent coating means having a thermal drop thereacross while in contact with tissue that is not substantially greater than 50 C.
for tissue temperatures within the range from about 1 000C to about 500 C.
4. Surgical apparatus for non-adherently contacting tissue to heat the tissue in contact therewith to an elevated temperature at which hemostasiswith minimal tissue damage occurs, comprising;
heating means operable at an elevated temperature for heating the tissue; and
non-adherent coating means disposed to be intermediate the heating means and the tissue being heated thereby; said non-adherent coating means having a maximum allowed thickness, t, in centimeters as given by the relationship: 50 ~ k
(qua) where k is thermal conductivity of the non-adherent coating in watts/cm0C., and O/A is the heat flux in watts/cm2.
5. Surgical apparatus according to any of claims 1 to 4 wherein the non-adherent coating means includes a composition selected from fluorocarbon polymers and silicone polymers.
6. Surgical apparatus according to any one of claims 1 to 4 wherein the non-adherent coating means includes a composition selected from organic phosphates and metallic fluorides.
7. A method of preventing adherence of surgical apparatus to tissue at an elevated temperature at which hemostasis with minimal tissue damage occurs, the method comprising the steps of:
transferring heat to the tissue from the surgical apparatus; and
interposing between the tissue and the surgical apparatus a non-adherent coating having a thickness which is not substantially greater than .0025 cm.
8. A method of preventing adherence of surgical apparatus to tissue at an elevated temperature at which hemostasis with minimal tissue damage occurs, the method comprising the steps of:
transferring heat to the tissue from the surgical apparatus; and
interposing between the tissue and the surgical apparatus a non-adherent coating having a maximum allowed thickness, t, in centimeters as given by the relationship: 50 ~ k
(via) where k is thermal conductivity of the non-adherent coating in watts/cm C., and QIA is the heat flux in watts/cm2.
9. A method of preventing adherence of surgical apparatus to tissue at an elevated temperature at which hemostasis with minimal tissue damage occurs, the method comprising the steps of:
transferring heat to the tissue from the surgical apparatus; and
interposing between the tissue and the surgical apparatus a non-adherent coating having a thermal impedance which is not substantially greater than 5 cm2 watt
10. A me.l1odi of preventing adherence of surgical apparatusto tissue at an elevated temperature at which hemostasis with minimal tissue damage occurs, the method comprising the steps of:
transferring heat to the tissue from the surgical apparatus; and
interposing between the tissue and the surgical apparatus a non-adherent coating having a thermal drop thereacross while in contact with tissue that is not substantially greater than 50 C. for tissue temperatures within the range from about 100 C to about 500 C.
11. Surgical apparatus substantially as hereinbefore described with reference to the accompanying drawings.
12. A method of preventing adherence of surgical tissue at an elevated temperature at which
hemostasis with minimal tissue damage occurs,
substantially as hereinbefore described with refer
ence to the accompanying drawings.
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US7392779A | 1979-09-10 | 1979-09-10 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| GB2060397A true GB2060397A (en) | 1981-05-07 |
| GB2060397B GB2060397B (en) | 1984-06-20 |
Family
ID=22116637
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| GB8028064A Expired GB2060397B (en) | 1979-09-10 | 1980-08-29 | Non-adherent surgical instrument and method |
Country Status (10)
| Country | Link |
|---|---|
| JP (1) | JPS5645648A (en) |
| AU (1) | AU6166380A (en) |
| BR (1) | BR8005831A (en) |
| CA (1) | CA1161326A (en) |
| DE (1) | DE3031049A1 (en) |
| FR (1) | FR2469174A1 (en) |
| GB (1) | GB2060397B (en) |
| NL (1) | NL8004670A (en) |
| SE (1) | SE449431B (en) |
| ZA (1) | ZA804849B (en) |
Cited By (17)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO1985002002A1 (en) * | 1983-11-01 | 1985-05-09 | Gardner Bros. & Perrott (W.A.) Pty. Ltd. | Descaling process |
| WO1985002335A1 (en) * | 1983-12-01 | 1985-06-06 | Kharkovsky Nauchno-Issledovatelsky Institut Obsche | Electrosurgical instrument |
| WO1985002336A1 (en) * | 1983-12-01 | 1985-06-06 | Kharkovsky Nauchno-Issledovatelsky Institut Obsche | Electrosurgical instrument |
| WO1985002762A1 (en) * | 1983-12-21 | 1985-07-04 | Kharkovsky Nauchno-Issledovatelsky Institut Obsche | Bipolar electrocoagulator |
| EP0157593A2 (en) * | 1984-03-28 | 1985-10-09 | CODMAN & SHURTLEFF INC. | Laser instrument |
| US4682596A (en) * | 1984-05-22 | 1987-07-28 | Cordis Corporation | Electrosurgical catheter and method for vascular applications |
| US4686981A (en) * | 1983-03-28 | 1987-08-18 | Laszlo Forintos | Surgical instrument especially for performing neurosurgical operations |
| FR2594322A1 (en) * | 1986-02-17 | 1987-08-21 | Cleef Jean Francois Van | Composite needle for single-pole electrocoagulation |
| US5000752A (en) * | 1985-12-13 | 1991-03-19 | William J. Hoskin | Treatment apparatus and method |
| USRE33925E (en) * | 1984-05-22 | 1992-05-12 | Cordis Corporation | Electrosurgical catheter aned method for vascular applications |
| WO1994009714A1 (en) * | 1992-11-04 | 1994-05-11 | Charles Edward Taylor | Electrically operated heating tool |
| US5348552A (en) * | 1991-08-30 | 1994-09-20 | Hoya Corporation | Laser surgical unit |
| WO1996020652A1 (en) * | 1994-12-30 | 1996-07-11 | Valleylab, Inc. | Partially coated electrodes, manufacture and use |
| WO1997011649A1 (en) * | 1995-09-27 | 1997-04-03 | Valleylab Inc. | Coated electrosurgical electrode and method of manufacture |
| WO2001008570A1 (en) * | 1999-07-30 | 2001-02-08 | Drukker International Bv | A cutting blade for a surgical instrument |
| US6511479B2 (en) | 2000-02-28 | 2003-01-28 | Conmed Corporation | Electrosurgical blade having directly adhered uniform coating of silicone release material and method of manufacturing same |
| US8372072B2 (en) | 2003-02-04 | 2013-02-12 | Cardiodex Ltd. | Methods and apparatus for hemostasis following arterial catheterization |
Families Citing this family (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4481057A (en) * | 1980-10-28 | 1984-11-06 | Oximetrix, Inc. | Cutting device and method of manufacture |
| US4501951A (en) * | 1982-08-16 | 1985-02-26 | E. I. Du Pont De Nemours And Company | Electric heating element for sterilely cutting and welding together thermoplastic tubes |
| US4534347A (en) * | 1983-04-08 | 1985-08-13 | Research Corporation | Microwave coagulating scalpel |
| JPS6065093A (en) * | 1983-09-21 | 1985-04-13 | Res Assoc Petroleum Alternat Dev<Rapad> | Treatment of oil sand oil and residual oil |
| US4886582A (en) * | 1988-06-29 | 1989-12-12 | Union Oil Company Of California | Resid hydroprocessing catalyst and method of preparation |
| JPH0375053A (en) * | 1989-08-18 | 1991-03-29 | Muranaka Iryoki Kk | Bipolar electrically solidifying tweezers |
| US5330471A (en) * | 1991-06-07 | 1994-07-19 | Hemostatic Surgery Corporation | Bi-polar electrosurgical endoscopic instruments and methods of use |
| US8366706B2 (en) | 2007-08-15 | 2013-02-05 | Cardiodex, Ltd. | Systems and methods for puncture closure |
| CN102805663A (en) * | 2012-07-06 | 2012-12-05 | 华中科技大学同济医学院附属同济医院 | Operative instrument with mechanical cutting and hemostasis functions |
| US11191586B2 (en) * | 2019-07-02 | 2021-12-07 | Jamison Alexander | Removable tip for use with electrosurgical devices |
Family Cites Families (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5063994U (en) * | 1973-10-09 | 1975-06-10 | ||
| BR7601564A (en) * | 1975-03-14 | 1976-09-14 | R Shaw | INSTRUMENT AND PROCESS FOR PERFORMING SURGICAL CUTS |
| US4091813A (en) * | 1975-03-14 | 1978-05-30 | Robert F. Shaw | Surgical instrument having self-regulated electrical proximity heating of its cutting edge and method of using the same |
| JPS539031A (en) * | 1976-07-13 | 1978-01-27 | Takenaka Komuten Co | Continuous sedimentation disposal equipment for highhmoisture sludge |
-
1980
- 1980-08-06 CA CA000357735A patent/CA1161326A/en not_active Expired
- 1980-08-08 ZA ZA00804849A patent/ZA804849B/en unknown
- 1980-08-16 DE DE19803031049 patent/DE3031049A1/en not_active Withdrawn
- 1980-08-19 NL NL8004670A patent/NL8004670A/en not_active Application Discontinuation
- 1980-08-22 AU AU61663/80A patent/AU6166380A/en not_active Abandoned
- 1980-08-29 GB GB8028064A patent/GB2060397B/en not_active Expired
- 1980-09-08 FR FR8019347A patent/FR2469174A1/en active Granted
- 1980-09-09 JP JP12523780A patent/JPS5645648A/en active Granted
- 1980-09-09 SE SE8006253A patent/SE449431B/en not_active IP Right Cessation
- 1980-09-10 BR BR8005831A patent/BR8005831A/en unknown
Cited By (28)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4686981A (en) * | 1983-03-28 | 1987-08-18 | Laszlo Forintos | Surgical instrument especially for performing neurosurgical operations |
| WO1985002002A1 (en) * | 1983-11-01 | 1985-05-09 | Gardner Bros. & Perrott (W.A.) Pty. Ltd. | Descaling process |
| US4657017A (en) * | 1983-12-01 | 1987-04-14 | Nauchno-Isledovatelsky Institute Obshei I Neotlozhnoi Khirugii | Electrosurgical instrument |
| WO1985002335A1 (en) * | 1983-12-01 | 1985-06-06 | Kharkovsky Nauchno-Issledovatelsky Institut Obsche | Electrosurgical instrument |
| WO1985002336A1 (en) * | 1983-12-01 | 1985-06-06 | Kharkovsky Nauchno-Issledovatelsky Institut Obsche | Electrosurgical instrument |
| GB2158722A (en) * | 1983-12-01 | 1985-11-20 | Kh Nii Obschei Neotlozh Khirug | Electrosurgical instrument |
| GB2158723A (en) * | 1983-12-01 | 1985-11-20 | Kh Nii Obschei Neotlozh Khirug | Electrosurgical instrument |
| US4637390A (en) * | 1983-12-01 | 1987-01-20 | Nauchno-Issledovatelsky Institut Obschei i Neotlozhno Khirurgii | Electrosurgical instrument |
| WO1985002762A1 (en) * | 1983-12-21 | 1985-07-04 | Kharkovsky Nauchno-Issledovatelsky Institut Obsche | Bipolar electrocoagulator |
| GB2161081A (en) * | 1983-12-21 | 1986-01-08 | Kh Nii Obschei Neot Khirurg | Bipolar electrocoagulator |
| US4637392A (en) * | 1983-12-21 | 1987-01-20 | Kharkovsky Nauchno-Issledovatelsky Institut Obschei I Neotlozhnoi Khirurgii | Bipolar electrocoagulator |
| US4580558A (en) * | 1984-03-28 | 1986-04-08 | Codman & Shurtleff, Inc. | Laser instrument |
| EP0157593A2 (en) * | 1984-03-28 | 1985-10-09 | CODMAN & SHURTLEFF INC. | Laser instrument |
| EP0157593A3 (en) * | 1984-03-28 | 1987-08-26 | Codman & Shurtleff Inc. | Laser instrument |
| US4682596A (en) * | 1984-05-22 | 1987-07-28 | Cordis Corporation | Electrosurgical catheter and method for vascular applications |
| USRE33925E (en) * | 1984-05-22 | 1992-05-12 | Cordis Corporation | Electrosurgical catheter aned method for vascular applications |
| US5000752A (en) * | 1985-12-13 | 1991-03-19 | William J. Hoskin | Treatment apparatus and method |
| FR2594322A1 (en) * | 1986-02-17 | 1987-08-21 | Cleef Jean Francois Van | Composite needle for single-pole electrocoagulation |
| US5348552A (en) * | 1991-08-30 | 1994-09-20 | Hoya Corporation | Laser surgical unit |
| US5695493A (en) * | 1991-08-30 | 1997-12-09 | Hoya Corporation | Laser surgical unit |
| WO1994009714A1 (en) * | 1992-11-04 | 1994-05-11 | Charles Edward Taylor | Electrically operated heating tool |
| WO1996020652A1 (en) * | 1994-12-30 | 1996-07-11 | Valleylab, Inc. | Partially coated electrodes, manufacture and use |
| WO1997011649A1 (en) * | 1995-09-27 | 1997-04-03 | Valleylab Inc. | Coated electrosurgical electrode and method of manufacture |
| AU717898B2 (en) * | 1995-09-27 | 2000-04-06 | Covidien Ag | Coated electrosurgical electrode and method of manufacture |
| EP1330990B1 (en) * | 1995-09-27 | 2005-10-12 | Sherwood Services AG | Coated electrosurgical electrode |
| WO2001008570A1 (en) * | 1999-07-30 | 2001-02-08 | Drukker International Bv | A cutting blade for a surgical instrument |
| US6511479B2 (en) | 2000-02-28 | 2003-01-28 | Conmed Corporation | Electrosurgical blade having directly adhered uniform coating of silicone release material and method of manufacturing same |
| US8372072B2 (en) | 2003-02-04 | 2013-02-12 | Cardiodex Ltd. | Methods and apparatus for hemostasis following arterial catheterization |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5645648A (en) | 1981-04-25 |
| CA1161326A (en) | 1984-01-31 |
| SE8006253L (en) | 1981-03-11 |
| AU6166380A (en) | 1981-03-19 |
| GB2060397B (en) | 1984-06-20 |
| FR2469174A1 (en) | 1981-05-22 |
| BR8005831A (en) | 1981-03-24 |
| JPH0334939B2 (en) | 1991-05-24 |
| FR2469174B3 (en) | 1982-04-23 |
| NL8004670A (en) | 1981-03-12 |
| DE3031049A1 (en) | 1981-04-02 |
| ZA804849B (en) | 1981-08-26 |
| SE449431B (en) | 1987-05-04 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PCNP | Patent ceased through non-payment of renewal fee |