ES2233239T3 - Instrumento electroquirurgico. - Google Patents
Instrumento electroquirurgico.Info
- Publication number
- ES2233239T3 ES2233239T3 ES00110410T ES00110410T ES2233239T3 ES 2233239 T3 ES2233239 T3 ES 2233239T3 ES 00110410 T ES00110410 T ES 00110410T ES 00110410 T ES00110410 T ES 00110410T ES 2233239 T3 ES2233239 T3 ES 2233239T3
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- 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
- A61B18/14—Probes or electrodes therefor
- A61B18/1485—Probes or electrodes therefor having a short rigid shaft for accessing the inner body through natural openings
-
- 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
-
- 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
- A61B18/14—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
- A61B18/12—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
- A61B18/14—Probes or electrodes therefor
- A61B18/1402—Probes for open surgery
-
- 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
- A61B18/14—Probes or electrodes therefor
- A61B18/1482—Probes or electrodes therefor having a long rigid shaft for accessing the inner body transcutaneously in minimal invasive surgery, e.g. laparoscopy
-
- 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
- A61B18/14—Probes or electrodes therefor
- A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
-
- 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
- A61B2018/1246—Generators therefor characterised by the output polarity
- A61B2018/126—Generators therefor characterised by the output polarity bipolar
-
- 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
- A61B18/14—Probes or electrodes therefor
- A61B2018/1472—Probes or electrodes therefor for use with liquid electrolyte, e.g. virtual electrodes
Abstract
Instrumento electroquirúrgico para el secado de tejidos (80) en presencia de un medio fluido eléctricamente conductor (78), comprendiendo el instrumento un cuerpo (12), un vástago alargado (30) y, en un extremo distal del vástago, un conjunto de electrodo (32), de manera que el conjunto del electrodo comprende un único electrodo activo (34) que tiene una parte de tratamiento de tejidos expuesta (34A), un electrodo de retorno (38) separado de la parte de tratamiento de tejidos por un elemento de aislamiento (36), poseyendo el electrodo de retorno una superficie de contacto de fluido retrasada en dirección longitudinal del instrumento desde la parte de tratamiento del electrodo activo y desde el extremo distal del elemento de aislamiento, siendo el conjunto del electrodo tal que cuando la parte de tratamiento de los tejidos se lleva a una posición adyacente a una superficie de tejidos sumergida en el medio fluido, la superficie de contacto con el fluido se encuentra separada con respecto a lasuperficie del tejido y el medio fluido completa una trayectoria de conducción entre el electrodo activo y el electrodo de retorno; de manera que la longitud de la trayectoria de conducción más corta a través del medio fluido entre la superficie de contacto del fluido del electrodo de retorno y la parte expuesta del electrodo activo es como mínimo de 1mm; y la proporción del área de la superficie del electrodo de retorno con respecto al área de la superficie del electrodo activo se encuentra en una gama comprendida desde 5:1 a 40:1.
Description
Instrumento electroquirúrgico.
La presente invención se refiere a un instrumento
electroquirúrgico para el tratamiento de tejidos en presencia de un
fluido conductor eléctrico y se refiere asimismo a un aparato de
sistema electroquirúrgico que incluye el mencionado instrumento.
La electrocirugía endoscópica es útil para el
tratamiento de tejidos en cavidades del cuerpo humano y se lleva a
cabo normalmente en presencia de un medio de distensión. Cuando el
medio de distensión es un líquido, se hace referencia habitualmente
a éste como electrocirugía bajo el agua, término que indica
electrocirugía en la que se efectúa el tratamiento de tejidos vivos
utilizando un instrumento de electrocirugía con un electrodo o
electrodos de tratamiento sumergidos en líquido en el lugar de la
operación. Un medio gaseoso se utiliza habitualmente cuando se lleva
a cabo cirugía endoscópica en una cavidad corporal distendible de
mayor volumen potencial, en el que un medio líquido no sería
apropiado, tal como es frecuentemente el caso de cirugía
laparoscópica o gastroenterológica.
La cirugía bajo agua se lleva a cabo
habitualmente utilizando técnicas endoscópicas, en las que el mismo
endoscopio puede proporcionar un conducto (al que se hace
habitualmente referencia como canal de trabajo) para el paso de un
electrodo. De manera alternativa, el endoscopio puede ser adaptado
de manera específica (tal como en un resectoscopio) para incluir
medios de montaje de un electrodo, o bien el electrodo puede ser
introducido en la cavidad corporal con intermedio de un dispositivo
de acceso separado con un ángulo con respecto al endoscopio, técnica
a la que se hace referencia habitualmente como triangulación. Estas
variaciones de técnica se pueden dividir por especialidad
quirúrgica, teniendo una u otra de las técnicas ventajas específicas
dada la ruta de acceso a la cavidad corporal específica. Se utilizan
en general endoscopios con canales de trabajo integrales o
endoscopios caracterizados como resectoscopios, cuando la cavidad
del cuerpo puede ser accedida a través de una abertura habitual del
cuerpo, tal como el canal cervical para tener acceso a la cavidad
endométrica del útero, o la uretra para acceder a la glándula
prostática y a la vejiga. Se hace referencia a los endoscopios
especialmente diseñados para su utilización en la cavidad
endométrica como histeroscopios y los diseñados para su utilización
en el aparato urinario incluyen cistoscopios, uretroscopios y
resectoscopios. Los procedimientos de resección o vaporización
transuretral de la glándula prostática se conocen respectivamente
como TURP y EVAP. Cuando no hay abertura natural del cuerpo a través
de la cual se pueda hacer pasar un endoscopio, se utiliza
habitualmente la técnica de triangulación. La triangulación se
utiliza habitualmente durante cirugía endoscópica bajo agua en
cavidades de las articulaciones, tales como las de la rodilla o del
hombro. El endoscopio utilizado en estos procesos recibe
frecuentemente la designación de artroscopio.
Se lleva a cabo habitualmente electrocirugía
utilizando un instrumento monopolar o un instrumento bipolar. Con la
electrocirugía monopolar se utiliza un electrodo activo en la zona
operativa y se fija una placa de retorno de conducción a la piel del
paciente. Con esta disposición, la corriente pasa desde el electrodo
activo a través de los tejidos del paciente hacia la placa de
retorno externa. Dado que el paciente representa una parte
significativa del circuito, los niveles de entrada de potencia
tienen que ser elevados (de modo típico 150 a 250 vatios), para
compensar la corriente resistiva que limita los tejidos del paciente
y en el caso de electrocirugía bajo el agua, las pérdidas de
potencia debidas al medio fluido que se vuelve parcialmente
conductor por la presencia de sangre u otros fluidos corporales. La
utilización de alta potencia con un dispositivo monopolar es también
peligroso, debido a que tiene lugar el calentamiento de los tejidos
en la placa de retorno, lo que puede provocar graves quemaduras en
la piel. También existe el riesgo de acoplamiento capacitivo entre
el instrumento y los tejidos del paciente en el punto de entrada en
la cavidad corporal.
Con electrocirugía bipolar, un par de electrodos
(un electrodo activo y un electrodo de retorno) se utilizan
conjuntamente en el lugar de aplicación en los tejidos. Esta
disposición tiene ventajas desde el punto de vista de la seguridad,
debido a la relativa proximidad de los dos electrodos de manera que
las corrientes de radio frecuencia quedan limitadas a la zona
existente entre los electrodos. No obstante, la profundidad del
efecto está directamente relacionada con la distancia entre los dos
electrodos y en aplicaciones que requieren electrodos muy pequeños,
la separación entre los electrodos resulta muy pequeña, limitando de
esta manera el efecto de los tejidos y la potencia de salida. La
separación de los electrodos entre sí dificultaría frecuentemente la
visión del lugar de aplicación y requeriría la modificación de la
técnica quirúrgica para asegurar un contacto directo de ambos
electrodos con el tejido.
Existe una serie de variaciones en el diseño
básico de la sonda bipolar. Por ejemplo, la descripción de la
Patente USA 4706667 describe uno de los fundamentos de diseño, es
decir, la proporción de áreas de contacto del electrodo de retorno y
del electrodo activo superior a 7:1 y menor de 20:1 para finalidades
de corte. Esta gama de valores se refiere solamente a
configuraciones de electrodo de corte. Cuando se utiliza un
instrumento bipolar para secado o para coagulación, la proporción de
las áreas de contacto de los dos electrodos se puede reducir
aproximadamente a 1:1 para evitar esfuerzos eléctricos diferenciales
en la zona de contacto entre el tejido y el electrodo.
La unión eléctrica entre el electrodo de retorno
y el tejido puede quedar soportada por humedecimiento del tejido por
una solución conductora tal como una solución salina normal. Esto
asegura que el efecto quirúrgico queda limitado a la aguja o
electrodo activo, completándose el circuito eléctrico entre los dos
electrodos por el tejido. Una de las evidentes limitaciones con el
diseño es que la aguja debe quedar completamente enterrada en los
tejidos para posibilitar que el electrodo de retorno complete el
circuito. Otro problema es un problema de orientación: incluso un
cambio relativamente reducido en el ángulo de aplicación desde el
contacto ideal perpendicular con respecto a la superficie de los
tejidos cambiará la proporción de área de contacto, de manera que
puede ocurrir un efecto quirúrgico en los tejidos en contacto con el
electrodo de retorno.
La distensión de la cavidad proporciona espacio
para tener acceso al lugar de la operación, para mejorar la
visualización y para permitir la manipulación de los instrumentos.
En cavidades corporales de bajo volumen, particularmente en el caso
de que es deseable distender la cavidad con una presión más elevada,
se utiliza más habitualmente líquido en vez de gas, debido a las
mejores características ópticas y por la razón de que retira o aleja
la sangre del lugar de operación.
Se ha llevado a cabo electrocirugía bajo agua
convencional, utilizando un líquido no conductor como irrigante (tal
como glicina al 1,5%), o como medio de distensión para eliminar
pérdidas por conducción eléctrica. La glicina es utilizada en
concentraciones isotónicas para impedir cambios osmóticos en la
sangre cuando tiene lugar la absorción intravascular. En el curso de
la operación se pueden cortar venas, con la infusión resultante del
líquido en la circulación, lo que puede provocar, entre otros
efectos, la dilución del sodio del suero, lo cual puede conducir a
las condiciones conocidas como intoxicación por agua.
Los solicitantes han descubierto que es posible
utilizar un medio líquido conductor, tal como una solución salina
normal, en electrocirugía endoscópica bajo el agua en lugar de
soluciones no conductoras libres de electrolitos. Una solución
salina normal es el medio de distensión preferente en cirugía
endoscópica bajo el agua cuando no se prevé electrocirugía o bien
cuando se utiliza un efecto de tejidos no eléctricos tales como un
tratamiento láser. Si bien una solución salina normal (0,9%
peso/volumen; 150mmol/l) tiene una conductividad eléctrica algo
superior a la de la mayor parte de tejidos corporales, tiene la
ventaja de que el desplazamiento por absorción o extravasado del
lugar de operación produce pocos efectos fisiológicos y se evitan
los efectos llamados de intoxicación por agua de las soluciones no
conductoras libres de electrolitos.
Los solicitantes han desarrollado un instrumento
bipolar adecuado para electrocirugía bajo el agua, utilizando un
medio líquido conductor según se define en la reivindicación 1
adjunta a esta descripción.
La estructura de electrodo de este instrumento en
combinación con un fluido electroconductor evita fundamentalmente
los problemas experimentados con la electrocirugía monopolar o
bipolar. En particular, los niveles de potencia introducida son
mucho más bajos que los necesarios generalmente con un dispositivo
monopolar (típicamente 100 vatios). Además, dada la separación
relativamente grande entre sus electrodos, se obtiene una
profundidad de efecto mejorada en comparación con dispositivos
bipolares convencionales.
Los documentos USA 4.706 667 y WO93/19681
describen instrumentos electroquirúrgicos, cada uno de los cuales
tiene un electrodo activo que no se utiliza únicamente para cortar
tejidos. Ninguno de los instrumentos utiliza un electrodo activo
para secado o coagulación de tejidos.
La presente invención se describirá a
continuación a título de ejemplo haciendo referencia a los dibujos,
en los cuales:
La figura 1 es un diagrama que muestra un sistema
electroquirúrgico de acuerdo con la invención;
La figura 2 es una vista lateral de una parte de
un instrumento electroquirúrgico que forma parte del sistema de la
figura 1;
La figura 3 es una sección transversal de una
parte de un instrumento electroquirúrgico alternativo de acuerdo con
la invención, cuyo instrumento está seccionado según un eje
longitudinal;
La figura 4 es un gráfico que muestra la
histéresis de la impedancia de carga eléctrica y potencia en radio
frecuencia disipada que tiene lugar en la utilización de un
instrumento de acuerdo con la invención en modalidades de secado y
vaporización;
La figura 5 es un diagrama de bloques del
generador del sistema electroquirúrgico mostrado en la figura 1;
La figura 6 es una vista lateral esquemática del
instrumento de la figura 3 que muestra la utilización del
instrumento para eliminación de tejidos por vaporización;
La figura 7 es una vista lateral esquemática de
un instrumento similar al mostrado en la figura 6, mostrando la
utilización del instrumento para secado o coagulación de tejidos;
y
Las figuras 8, 9 y 10 son vistas laterales de
otros instrumentos electroquirúrgicos de acuerdo con la invención,
mostrando diferentes configuraciones de electrodos y de
aislante;
Haciendo referencia a los dibujos, la figura 1
muestra un aparato electroquirúrgico que incluye un generador
electroquirúrgico (10) que tiene un enchufe de salida (10S) que
proporciona una salida de radio frecuencia (RF) para un instrumento
bipolar, en forma de un útil manual (2) y un electrodo desmontable
(28), con intermedio de un cable de conexión (14). La activación del
generador (10) se puede llevar a cabo a partir de la unidad manual
(12) mediante una conexión de control en el cable (14) o por medio
de un interruptor o pedal de pie (16), tal como se ha mostrado,
conectado separadamente a la parte posterior del generador (10)
mediante un cable de conexión (18) para un interruptor de pedal. En
la realización mostrada, la unidad (16) del interruptor de pedal
tiene dos interruptores de pedal (16A) y (16B) para seleccionar
modalidades de secado y de vaporización del generador (10)
respectivamente. El panel frontal del generador tiene botones
pulsadores (20) y (22) para ajustar respectivamente los niveles de
potencia de secado y vaporización, lo cual está indicado en la
pantalla (24).
Los botones pulsadores (26) están dispuestos como medios alternativos para selección entre las modalidades de secado y vaporización.
Los botones pulsadores (26) están dispuestos como medios alternativos para selección entre las modalidades de secado y vaporización.
No es necesario que el instrumento incluya un
dispositivo manual, sino que simplemente puede incluir un conector
para el montaje a otro dispositivo tal como un resectoscopio. En la
figura 1, el instrumento tiene una unidad de electrodo (28) que se
ha mostrado montada en la pieza o unidad manual (12).
La unidad de electrodo (E) puede adoptar una
serie de formas distintas, algunas de las cuales se han descrito a
continuación.
En una configuración básica, mostrada en la
figura 2, una unidad de electrodo para fijación desmontable a una
unidad manual comprende un eje (30) que puede ser un tubo conductor
cubierto con una funda aislante (30S), con un conjunto de electrodo
(32) en un extremo distal del vástago o eje (30). En el otro extremo
del vástago (no mostrado) se disponen medios para conectar la unidad
de manera tanto mecánica como eléctrica a un útil manual.
El conjunto de electrodo (32) comprende un
electrodo central activo (34) que está expuesto en el extremo distal
de la unidad formando una parte de tratamiento del electrodo.
Preferentemente, el electrodo activo es un cable metálico que se
extiende en forma de conductor central a través del conjunto del eje
(30) hasta un contacto en el extremo próximo (no mostrado en el
dibujo). Rodeando el electrodo (34) y el conductor interno se
encuentra un manguito aislante (36) cuyo extremo distal está
expuesto de forma próxima a la parte de tratamiento expuesta del
electrodo (34). De manera típica, este manguito está realizado a
base de un material cerámico para resistir averías por formación del
arco. Rodeando el manguito (36) se encuentra el electrodo de retorno
(38) en forma de un tubo metálico que es integral eléctricamente (y
opcionalmente también de forma mecánica) con el cuerpo del tubo
metálico del eje (30). Este electrodo de retorno termina en un punto
próximo al extremo del manguito (36) de manera que queda retirado
con respecto a la zona de tratamiento expuesta del electrodo activo
(34) y queda separado tanto radial como axialmente con respecto a
esta última. Se observará que, principalmente debido a un diámetro
mucho más grande del electrodo de retorno en comparación con el del
electrodo activo, el electrodo de retorno proporciona una superficie
de contacto de fluido expuesta o visible que tiene un área
superficial mucho mayor que la de la parte de tratamiento del
electrodo activo expuesta o visible. La envolvente de aislamiento
(30S) termina en el lugar que está separado con poca distancia con
respecto al extremo distal del electrodo de retorno (38) a efectos
de proporcionar el área superficial requerida para la superficie de
contacto con el fluido del electrodo de retorno. En el extremo
distal de la unidad del electrodo, el diámetro del conductor de
retorno se encuentra de manera típica entre valores aproximados de 1
mm a 5 mm. La dimensión de longitud de la superficie en contacto del
fluido de la parte expuesta o parte vista del electrodo de retorno
(38) se encuentra de manera típica entre valores de 1 mm y 5 mm,
mientras que la separación longitudinal con respecto al electrodo de
retorno (38) de la parte expuesta de tratamiento del electrodo
activo se encuentra entre 1 mm y 5 mm. Otros objetos de la
configuración y dimensionado de los conjuntos de los electrodos se
indicarán más adelante de forma más detallada.
En efecto, la estructura del electrodo mostrada
en la figura 2 es bipolar, de manera que solamente uno de los
electrodos (34) se prolonga realmente hasta el extremo distal de la
unidad. Esto significa que, en utilización normal, cuando el
conjunto del electrodo está sumergido en un medio fluido conductor,
el electrodo de retorno (38) permanece separado con respecto a los
tejidos sometidos a tratamiento y existe una trayectoria de
corriente entre los dos electrodos a través de los tejidos y del
medio fluido conductor que se encuentra en contacto con el electrodo
de retorno.
La separación axial de los electrodos permite una
estructura muy fina para los electrodos en términos de diámetro,
dado que la trayectoria de aislamiento es considerablemente más
larga que en un electrodo bipolar que tiene meramente una separación
radial entre superficies de electrodos expuestas o visibles. Esto
permite la utilización de potencias más elevadas que con estructuras
de electrodos convencionales, sin provocar un indeseable efecto de
arco o en el caso de corte electroquirúrgico o tratamiento de
vaporización sin provocar averías en la unidad del electrodo debido
a un excesivo efecto de arco a elevadas temperaturas.
La disposición desplazada que se ha mostrado
permite al cirujano la visión de la punta de electrodo de contacto
con los tejidos y permite una amplia gama de ángulos de aplicación
con respecto a la superficie del tejido, lo cual es particularmente
importante en los espacios confinados o limitados típicos de cirugía
endoscópica.
Haciendo referencia a la figura 3, una unidad de
electrodo alternativa para la fijación desmontable al útil manual
(12) del instrumento electroquirúrgico mostrado en la figura 1,
comprende un vástago (30) que está constituido por un tubo
semiflexible fabricado a base de acero inoxidable o de material
phynox con recubrimiento por electrólisis mediante cobre u oro, con
un conjunto de electrodo (32) en un extremo distal del mismo. En el
otro extremo del eje (30) (no mostrado) se disponen medios para
interconectar la unidad de electrodo al útil manual tanto de forma
mecánica como eléctrica.
El conjunto de electrodo (32) comprende un
electrodo de contacto central activo o de contacto con los tejidos
(34) que está realizado a base de platino, platino/iridio o
platino/tungsteno, y que está constituido por una punta expuesta o
visible (34A) de forma general hemisférica y un conductor central
integral (34B). El conductor (34B) está eléctricamente conectado a
un conductor central de cobre (34C) por fijación de un resorte
delgado de acero inoxidable (34D) sobre partes extremas adyacentes
de los conductores (34B) y (34C), proporcionando de esta manera una
conexión eléctrica entre el útil manual del instrumento y la punta
expuesta o visible (34A). Un manguito cerámico de aislamiento (36)
rodea el conductor (34B), el resorte (34D), y la parte extrema
adyacente del conductor de cobre (34C). El manguito (36) tiene una
parte expuesta o visible (36A) que rodea la parte del extremo distal
del conductor (34B). Un electrodo de retorno (38), que forma una
parte extrema distal del vástago (30), proporcionando una superficie
de contacto con el fluido de forma cilíndrica, rodea a poca
distancia el manguito (36) y se extiende al conductor de cobre (34C)
separado con respecto a aquél por el manguito de aislamiento (40).
Un recubrimiento externo de retracción térmica o poliamida y de
carácter aislante (30S) rodea el vástago (30) y la parte próxima del
electrodo de retorno (38).
Cuando se utiliza en combinación con el generador
electroquirúrgico mostrado en la figura 1, la unidad de electrodo de
la figura 3 puede ser utilizada en un medio fluido conductor para
eliminación de tejidos por vaporización, para el esculpido y
definición de contorno de los meniscos durante cirugía artroscópica
o para secado, dependiendo de la forma en la que se controla el
generador. La figura 4 muestra la forma en la que se puede controlar
el generador para aprovechar la histéresis que existe entre las
modalidades de secado y de vaporización de la unidad de electrodo.
Por lo tanto, suponiendo que el conjunto de electrodo (32) de la
unidad queda sumergido en un medio conductor tal como una solución
salina, existe una impedancia de carga inicial "r" en el punto
"O", cuya magnitud queda definida por la geometría del conjunto
del electrodo y la conductividad eléctrica del medio fluido. El
valor de "r" cambia cuando el electrodo activo (34) establece
contacto con los tejidos, de manera que cuanto mayor es el valor de
"r" mayor es la propensión del conjunto de electrodo (32) en
entrar en la modalidad de vaporización. Cuando se aplica potencia en
RF al conjunto de electrodos (32), el medio fluido se calienta.
Suponiendo que el medio fluido sea solución salina normal (0,9%
peso/volumen), el coeficiente de temperatura de la conductividad del
medio fluido es positivo, de manera que el correspondiente
coeficiente de impedancia es negativo. Por lo tanto, al aplicar
potencia, la impedancia disminuye inicialmente y continúa
disminuyendo al aumentar la potencia de disipación hasta el punto
"B", en cuyo punto la solución salina en contacto íntimo con el
conjunto del electrodo (32) llega a su punto de ebullición. Pequeñas
burbujas de vapor se forman sobre la superficie de la punta activa
(34A) y entonces la impedancia empieza a aumentar. Después del punto
"B", al aumentar adicionalmente la disipación de la potencia,
el coeficiente de potencia positivo de la impedancia predomina, de
manera que el incremento de la potencia comporta en este caso un
incremento de la impedancia.
Dado que se forma una bolsa de vapor a partir de
las burbujas de vapor, existe un incremento en la densidad de
potencia en el interfaz residual electrodo/solución salina. No
obstante, existe un área expuesta o visible de la punta (34A) del
electrodo activo que no está cubierta por burbujas de vapor y esto
aumenta o refuerza el interfaz, produciendo una cantidad mayor de
burbujas de vapor, y por lo tanto, una densidad superior de
potencia. Éste es un estado de inexistencia de control
("run-away"), con un punto de equilibrio que
tiene lugar solamente cuando el electrodo está completamente
envuelto en vapor de agua. Para un conjunto de variables
determinado, existe un umbral de potencia antes de que este nuevo
equilibrio pueda ser alcanzado (punto "C").
La zona del gráfico entre los puntos "B" y
"C" representa, por lo tanto, el límite superior de la
modalidad de secado. Una vez que se encuentre en el estado de
equilibrio de vaporización, la impedancia incrementa rápidamente
hasta un valor próximo a 1000 ohms, dependiendo el valor absoluto de
las variables del sistema. La bolsa de vapor es mantenida en esta
situación por descargas a través de la bolsa de vapor entre la punta
(34A) del electrodo activo y el interfaz vapor/solución salina. La
mayor parte de la disipación de potencia tiene lugar dentro de esta
bolsa, con un calentamiento consiguiente de la punta (34A). La
cantidad de energía disipada y las dimensiones de la bolsa dependen
del voltaje de salida. Si éste es demasiado bajo, la bolsa no se
mantendrá y, si es demasiado elevado, el conjunto del electrodo (32)
se destruirá. Por lo tanto, a efectos de impedir la destrucción del
conjunto del electrodo (32) se debe reducir la salida de potencia
del generador una vez que la impedancia ha alcanzado el punto
"D". Se debe observar que si la potencia no se reduce en este
momento, la curva potencia/impedancia continuará creciendo y podría
tener lugar la destrucción del electrodo.
La línea de trazos "E" indica el nivel de
potencia por encima del cual es inevitable la destrucción del
electrodo. Al reducir la potencia, la impedancia disminuye hasta que
en el punto "A" la bolsa de vapor se aplasta y el conjunto del
electrodo (32) vuelve a la modalidad de secado. En este punto, la
disipación de potencia dentro de la bolsa de vapor es insuficiente
para sostenerla, de manera que se restablece el contacto directo
entre la punta (34A) del electrodo activo y la solución salina, y la
impedancia disminuye de manera muy acusada. La densidad de potencia
en la punta (34A) disminuye también, de manera que la temperatura de
la solución salina disminuye por debajo del punto de ebullición. El
conjunto del electrodo (32) se encuentra entonces en una modalidad
de
secado estable.
secado estable.
El control de la potencia del generador para
conseguir funciones de secado, corte de tejidos y vaporización se
lleva a cabo detectando el voltaje máximo RF que aparece a través de
las conexiones de salida del generador y reduciendo rápidamente la
potencia de salida suministrada siempre que se alcance un voltaje
pico o máximo de umbral perfeccionado. Como mínimo en una modalidad
de secado, esta reducción de potencia es significativamente superior
que la requerida solamente para llevar el voltaje de salida pico o
máximo por debajo del umbral. Preferentemente, la reducción de
potencia es como mínimo 50% para aprovechar las características de
la histéresis descrita anteriormente con referencia a la figura
4.
Haciendo referencia a la figura 5, el generador
comprende un oscilador de potencia de radio frecuencia (RF) (60) que
tiene un par de conexiones de salida (60C) para acoplamiento con
intermedio de terminales de salida (62) a la impedancia de carga
(64) representada por el conjunto del electrodo cuando se encuentra
en utilización. La potencia es suministrada al oscilador (60) por un
suministro de potencia (66) con modalidad conmutada.
En la realización preferente, el oscilador RF
(60) funciona aproximadamente a 400 kHz, siendo factible cualquier
frecuencia a partir de 300 kHz hacia arriba hacia adentro de la gama
de frecuencias HF. El suministro de potencia en modalidad conmutada
funciona típicamente a una frecuencia comprendida en una gama de
valores de 25 a 50 kHz. Acoplado a través de las conexiones de
salida (60C) se encuentra un detector de voltaje umbral (68) que
tiene una primera salida (18A) acoplada al suministro (16) de
potencia en modalidad conmutada y una segunda salida (18B) acoplada
a un circuito de control de tiempo "on" (70).
Un controlador (72) del microprocesador acoplado a los controles y pantalla del operador (mostrados en la figura 1) está conectado a una entrada de control (66A) del suministro de potencia (66) para ajustar la potencia de salida del generador por medio de la variación del voltaje de suministro o de alimentación y hacia una entrada (68C) de ajuste de umbral del detector (68) del umbral de voltaje para ajustar los valores límite máximos de salida en RF.
Un controlador (72) del microprocesador acoplado a los controles y pantalla del operador (mostrados en la figura 1) está conectado a una entrada de control (66A) del suministro de potencia (66) para ajustar la potencia de salida del generador por medio de la variación del voltaje de suministro o de alimentación y hacia una entrada (68C) de ajuste de umbral del detector (68) del umbral de voltaje para ajustar los valores límite máximos de salida en RF.
En su funcionamiento, el controlador (72) del
microprocesador provoca la aplicación de potencia al suministro (66)
de potencia en modalidad conmutada cuando hay demanda de potencia
electroquirúrgica por parte del cirujano que hace funcionar un
dispositivo conmutador de activación que puede quedar dispuesto en
una unidad manual o interruptor de pie (ver figura 1). Un umbral de
voltaje de salida constante queda dispuesto independientemente del
voltaje de suministro a través de la entrada (68C) de acuerdo con
los ajustes de control en el panel frontal del generador (ver figura
1). De manera típica, para secado o coagulación, el umbral se
dispone en un valor umbral de secado entre 150 voltios y 200
voltios. Cuando se requiere una salida de corte o de vaporización,
el umbral se dispone en un valor en una gama de 250 o 300 voltios a
600 voltios. Estos valores de voltaje son valores máximos o valores
pico. El hecho de que sean valores máximo o valores pico significa
que para el secado como mínimo es preferible tener una forma de onda
de RF de salida con un bajo factor de cresta para proporcionar una
potencia máxima antes de que el voltaje sea fijado en los valores
determinados. De manera típica se consigue un valor de cresta de 1,5
o inferior.
Cuando se acciona por primera vez el generador,
la situación de la entrada de control (60I) del oscilador de RF (60)
(que está conectado al circuito de control de tiempo "on" (70)
(marcha)) se encuentra en marcha ("on"), de manera que el
dispositivo de conmutación de potencia que forma el elemento
oscilante del oscilador (60) es conmutado para un período de
conducción máxima durante cada ciclo de oscilación. La potencia
suministrada a la carga (64) depende parcialmente del voltaje de
alimentación aplicado al oscilador de RF (60) a partir del
suministro de potencia en modalidad conmutada (66) y parcialmente en
la impedancia de carga (64). Si el voltaje de suministro es
suficientemente elevado, la temperatura del medio líquido que rodea
los electrodos del instrumento electroquirúrgico (o dentro de un
medio gaseoso, la temperatura de líquido contenida dentro del
tejido) puede aumentar de manera tal que el medio líquido se
vaporiza, lo cual conduce a un incremento rápido en la impedancia de
carga y a un consiguiente incremento rápido en el voltaje de salida
aplicado en los terminales (12). Ésta es una situación poco deseable
si se requiere una salida de secado. Por esta razón, el umbral de
voltaje para una salida de secado se ajusta para provocar el envío
de señales de disparo al circuito de control de tiempo de marcha
"on" (70) y al suministro (66) de potencia en modalidad
conmutada cuando se alcanza el valor de umbral. El circuito (70) de
control de tiempo de marcha ("on") tiene el efecto de reducir
de manera virtualmente instantánea el tiempo "on" del
dispositivo de conmutación del oscilador RF. De manera simultánea,
el suministro de potencia en modalidad conmutada es desactivado de
manera que el voltaje suministrado al oscilador (60) empieza a
disminuir.
El voltaje de salida del generador es importante
para la modalidad de funcionamiento. En realidad, las modalidades de
salida se definen puramente por el voltaje de salida,
específicamente el voltaje de salida máximo o pico. El valor
absoluto del voltaje de salida es necesario solamente para control
de término múltiple. No obstante, un control simple de término único
(es decir, utilizando una variable de control) puede ser utilizado
en este generador a efectos de limitar o confinar el voltaje de
salida a límites de voltaje predeterminados. Por esta razón, el
detector (68) de voltaje umbral mostrado en la figura 5 compara el
voltaje de salida pico o máximo RF con un nivel de umbral
predeterminado en corriente continua y tiene un tiempo de respuesta
suficientemente rápido para producir un impulso de reposición para
el circuito de control de tiempo (70) en marcha ("on") dentro
de medio ciclo de RF.
La potencia máxima absorbida coincide con las
condiciones del electrodo existentes inmediatamente antes de la
formación de burbujas de vapor, puesto que esto coincide con una
disipación máxima de potencia en el área de electrodo humedecido
máxima. Por lo tanto es deseable que el electrodo permanezca en
estado húmedo para la potencia de secado máxima. La utilización de
detección del límite de voltaje comporta una reducción de potencia
que permite que las burbujas de vapor se aplasten, lo cual a su vez
aumenta la capacidad del electrodo activo en absorber potencia. Es
por esta razón que el generador incluye un bucle de control que
tiene un gran efecto multiplicador, por el hecho de que el estímulo
de realimentación de voltaje máximo cuando llega a un umbral
predeterminado provoca una gran reducción instantánea de potencia
provocando una reducción en el voltaje máximo de salida hasta un
nivel significativamente por debajo del nivel de voltaje de salida
máximo o pico ajustado por el detector de umbral (68). Este efecto
multiplicador o "overshoot" asegura el retorno al estado
humedecido requerido.
Se describen otros detalles del generador y su
funcionamiento en la solicitud de Patente británica Nº. 9604770.9
pendiente de la actual, el contenido de la cual se incorpora en esta
descripción a título de referencia.
Teniendo en cuenta lo anterior, quedará evidente
que la unidad de electrodo de la figura 3 puede ser utilizada para
secado haciendo trabajar la unidad en la zona del gráfico
comprendida entre el punto "0" y un punto en una zona entre los
puntos "B" y "C". En este caso, el conjunto del electrodo
(32) es introducido en un lugar funcional seleccionado con la punta
activa
(34A) adyacente a los tejidos a tratar y con los tejidos y punta activa y electrodo de retorno sumergidos en la solución salina. El generador es activado a continuación (y controlado de manera cíclica tal como se ha descrito anteriormente) para suministrar suficiente potencia al conjunto del electrodo (32) a efectos de mantener la solución salina adyacente a la punta activa (34A) en su punto de ebullición o justamente por debajo del mismo, sin crear una bolsa de vapor que rodee la punta activa. El conjunto del electrodo es manipulado de manera que provoca calentamiento y secado de los tejidos en una zona requerida adyacente a la punta activa (34A). La unidad del electrodo puede ser utilizada para vaporización en la zona del gráfico entre el punto "D" y la línea de trazos F que constituye el nivel por debajo del cual la vaporización no es estable. La parte superior de esta curva se utiliza para eliminación de tejidos por vaporización. En esta modalidad, una aplicación ligera del instrumento a los tejidos a tratar posibilita llevar a cabo el esculpido y conformado de los mismos.
(34A) adyacente a los tejidos a tratar y con los tejidos y punta activa y electrodo de retorno sumergidos en la solución salina. El generador es activado a continuación (y controlado de manera cíclica tal como se ha descrito anteriormente) para suministrar suficiente potencia al conjunto del electrodo (32) a efectos de mantener la solución salina adyacente a la punta activa (34A) en su punto de ebullición o justamente por debajo del mismo, sin crear una bolsa de vapor que rodee la punta activa. El conjunto del electrodo es manipulado de manera que provoca calentamiento y secado de los tejidos en una zona requerida adyacente a la punta activa (34A). La unidad del electrodo puede ser utilizada para vaporización en la zona del gráfico entre el punto "D" y la línea de trazos F que constituye el nivel por debajo del cual la vaporización no es estable. La parte superior de esta curva se utiliza para eliminación de tejidos por vaporización. En esta modalidad, una aplicación ligera del instrumento a los tejidos a tratar posibilita llevar a cabo el esculpido y conformado de los mismos.
El conjunto de electrodo (32) tiene
preferentemente electrodos unitarios con una proporción retorno:área
superficial del electrodo activo comprendida en una gama de valores
de 5:1 a 40:1 (es decir, la proporción de las áreas superficiales de
las zonas expuestas de los dos electrodos se encuentra dentro de
este campo de valores).
La figura 6 muestra la utilización de la unidad
de electrodo de la figura 3 para eliminación de tejidos por
vaporización, estando la unidad de electrodo sumergida en el fluido
conductor (78). De este modo, la unidad del electrodo crea una
densidad de energía suficientemente elevada en la punta activa (34A)
para vaporizar tejidos (80) y para crear una bolsa de vapor (82) que
rodea la punta activa. La formación de la bolsa de vapor (82) crea
aproximadamente un incremento de 10 veces de la impedancia de
contacto con el incremento subsiguiente del voltaje de salida. Se
crean arcos (84) en la bolsa de vapor (82) completando el circuito
al electrodo de retorno (38). El tejido (80) que entra en contacto
con la bolsa de vapor (82) representará una trayectoria de
resistencia eléctrica mínima para completar el circuito. Cuanto más
próximo llegue a estar el tejido (80) con respecto a la punta activa
(34A), mayor es la concentración de energía sobre los tejidos, hasta
el punto de que las células pueden explosionar al recibir la acción
de los arcos (84), a causa de la trayectoria de retorno a través del
fluido de conexión (solución salina en este caso) que queda
bloqueada por la barrera de alta impedancia de la bolsa de vapor
(82). La solución salina actúa asimismo disolviendo o dispersando
los productos sólidos de la vaporización.
En su utilización, el conjunto de electrodo (32)
es introducido en un lugar operativo seleccionado con la punta
activa (34A) del electrodo adyacente a los tejidos a vaporizar y con
los tejidos, punta activa y electrodo de retorno (38) sumergidos en
la solución salina (78). El generador RF es activado para
suministrar suficiente potencia (tal como se ha descrito
anteriormente con referencia a la figura 4) al conjunto de electrodo
(32) para vaporizar la solución salina y mantener una bolsa de vapor
rodeando el electrodo en contacto con los tejidos. Cuando se utiliza
la unidad de electrodo para el esculpido o conformado de meniscos
durante cirugía artroscópica, el conjunto de electrodo (32) es
aplicado con una presión ligera en el lugar de operación
seleccionado y es manipulado de manera que la superficie
parcialmente esférica de la punta activa (34A) se desplaza sobre la
superficie a tratar, suavizando los tejidos y en particular los
meniscos con una acción de esculpido o conformado.
La figura 7 muestra la utilización de una unidad
de electrodo similar a la de la figura 3 utilizada para el secado de
tejidos. En la modalidad de secado, la potencia de salida es
suministrada a los electrodos en una primera gama de salida, de
manera que la corriente pasa desde el electrodo activo (34) al
electrodo de retorno (38). Tal como se ha descrito anteriormente, la
potencia de salida provoca que la solución salina adyacente al
electrodo activo (34) se caliente, preferentemente hasta un punto
correspondiente al punto de ebullición o próximo al mismo de la
solución salina. Esto crea pequeñas burbujas de vapor sobre la
superficie del electrodo activo (14) que incrementa la impedancia
alrededor del electrodo activo (34).
El tejido corporal (80) tiene de manera típica
una impedancia más reducida que la impedancia de la combinación de
las burbujas de vapor y de la solución salina adyacente al electrodo
activo (34). Cuando un electrodo activo (34) rodeado por pequeñas
burbujas de vapor y solución salina es llevado a establecer contacto
con el tejido (80), dicho tejido (80) pasa a formar parte de la
trayectoria preferente para la corriente eléctrica. De acuerdo con
ello, la trayectoria preferente para la corriente sale del electrodo
activo (34) en el punto de contacto con los tejidos atraviesa el
tejido (80) y luego vuelve al electrodo de retorno (38) a través de
la solución salina, tal como se ha mostrado en la figura 7.
La invención tiene aplicación específica en el
secado de tejidos. Para el secado de tejidos, un método preferente
de actuación consiste en contactar solamente una parte del electrodo
activo con los tejidos, permaneciendo el resto del electrodo activo
alejado de los tejidos y rodeado por solución salina, de manera que
la corriente puede pasar desde el electrodo activo al de retorno, a
través de la solución salina, sin pasar a través de los tejidos. Por
ejemplo, en la realización mostrada en la figura 7, solamente la
parte distal del electrodo activo establece contacto con los
tejidos, de manera que la parte próxima permanece alejada de los
mismos.
La invención puede conseguir secado con una
carbonización mínima o nula de los tejidos. Cuando el electrodo
activo (34) establece contacto con el tejido (80), la corriente pasa
a través del tejido, provocando que éste se seque en el punto de
contacto y alrededor del mismo. El área y volumen de los tejidos
secados aumentan de manera generalmente radial hacia afuera desde el
punto de contacto.
En la realización mostrada en la figura 7, la
parte de tratamiento expuesta del electrodo activo (34) es más larga
que ancha. Esto permite que la punta del electrodo establezca
contacto con la superficie del tejido manteniendo simultáneamente la
mayor parte de la zona de tratamiento expuesta fuera de contacto con
el tejido, incluso cuando el instrumento queda dispuesto en ángulo
con respecto a la superficie del tejido. Dado que la mayor parte
expuesta del electrodo se encuentra fuera de contacto con el tejido,
la trayectoria de la corriente se desplazará de manera más fácil, en
el secado de un volumen de tejido suficiente, desde la trayectoria
que atraviesa el tejido a una trayectoria que pasa directamente
desde el electrodo activo a la solución salina.
En la unidad de electrodo mostrada en la figura
3, la parte expuesta del electrodo activo (34) es relativamente
corta en comparación con la longitud del elemento de aislamiento
(36) entre el electrodo activo (34) y el electrodo de retorno (38).
Con dicha configuración de electrodo, es aplicable el funcionamiento
biestable del instrumento inherente a la característica de
histéresis descrita anteriormente con referencia a la figura 4, por
el hecho de que el instrumento puede ser utilizado en una modalidad
de secado o en una modalidad de vaporización a baja potencia. En
algunas circunstancias, particularmente si la parte de tratamiento
expuesta del electrodo activo es larga, el funcionamiento biestable
puede ser difícil de conseguir.
A continuación se describirán medidas para
solucionar esta dificultad, haciendo referencia a la figura 8, que
muestra una unidad de electrodo que comprende un vástago (30)
constituido por un tubo semiflexible realizado a base de acero
inoxidable o de phynox recubierto electrolíticamente con un baño de
cobre o de oro, con un conjunto de electrodo (32) en su extremo
distal. El conjunto de electrodo (32) comprende un electrodo central
activo (34) que tiene una parte alargada de tratamiento expuesta
(34A) (a la que se hará referencia como electrodo de "aguja") y
un conductor central integral (34B). Un manguito de aislamiento
cerámico cilíndrico (36) rodea el conductor (34B) y un electrodo de
retorno (38), que está constituido por la parte distal extrema del
vástago (30), establece contacto con un extremo próximo del manguito
(36). Un recubrimiento de poliamida aislante externo (40) rodea la
parte próxima del vástago adyacente al electrodo de retorno (38),
proporcionando de esta manera al electrodo de retorno una superficie
de contacto anular con el fluido que se extiende desde el borde de
recubrimiento (40) al manguito de aislamiento (36). El manguito de
aislamiento (36) tiene una cara extrema distal (36A) de un diámetro
tal que el radio del escalón (es decir, la distancia entre el borde
circunferencial de la cara extrema (36A) y el diámetro externo del
electrodo activo (34)) es como mínimo 1/20 de la longitud de la
parte (34a) de tratamiento del electrodo activo expuesta o visible.
El manguito de aislamiento (36) tiene por lo tanto un acodamiento o
escalón que es coaxial con el electrodo activo (34). En su
utilización, este escalón evita la formación local del arco que
podría presentarse de otro modo en el extremo próximo de la parte
(34A) de tratamiento del electrodo activo expuesta o visible,
haciendo ineficaz el extremo distal de la parte de tratamiento
(34A).
Para considerar el funcionamiento del electrodo
de manera más detallada, cuando la unidad del electrodo funciona en
un corte de tejidos o en una modalidad de vaporización, se forma una
burbuja de vapor alrededor de la parte (34A) de tratamiento del
electrodo activo. Esta burbuja es mantenida por la formación de arco
dentro de la misma. Cuanto mayor es el voltaje aplicado, mayor es la
dimensión de la burbuja. La energía disipada por cada uno de los
arcos está limitada por la impedancia por el fluido restante en la
trayectoria de conducción y por la impedancia de origen del
generador. No obstante, un arco se comporta como impedancia negativa
por el hecho de que si la energía del arco es suficientemente
elevada, se forma una trayectoria ionizada de impedancia muy
reducida. Esto puede llevar a condiciones inestables de impedancia
de trayectoria ionizada cada vez más decreciente, excepto si la
impedancia del fluido entre la burbuja y el electrodo de retorno es
suficiente para actuar como límite de la potencia disipada. También
es posible que la bolsa de vapor alrededor de la parte de
tratamiento del electrodo activo rodee al electrodo de retorno. En
estas circunstancias, la energía del arco queda limitada solamente
por la impedancia de fuente del generador, pero esta limitación de
potencia es poco satisfactoria y no puede ser ajustada de acuerdo
con las dimensiones del electrodo. Por estas razones las dimensiones
y la configuración del manguito de aislamiento (36) deben ser tales
que definan una longitud mínima de la trayectoria de conducción de
1mm entre la parte (34A) de tratamiento del electrodo activo y la
superficie de contacto de fluido del electrodo de retorno (38). Esta
mínima longitud de trayectoria es, en el caso de la realización
mostrada en la figura 8, la longitud a del manguito (36) más
el radio c del escalón, tal como se muestra en la figura
8.
Otra consideración es la posibilidad de que se
forme una bolsa de vapor solamente sobre parte de la zona de
tratamiento expuesta (34A) del electrodo activo (34). Cuando el
voltaje aplicado y la potencia son suficientemente elevados, se
formará una bolsa de vapor alrededor de la parte de tratamiento
expuesta del electrodo activo. Preferentemente, la bolsa se forma de
manera uniforme sobre toda la longitud de la zona de tratamiento. En
esta situación, la impedancia de la carga presentada al generador
puede cambiar por un factor que puede llegar a 20. No obstante,
cuando hay diferencias significativas en la longitud de la
trayectoria de conducción entre la superficie de contacto del fluido
con el electrodo de retorno y las diferentes partes de la zona (34A)
de tratamiento del electrodo activo expuesta o visible, se establece
un gradiente de voltaje según la longitud de cada electrodo.
Preferentemente, la superficie de contacto del fluido es
suficientemente grande y tiene una proporción de aspecto tal que su
longitud es como mínimo tan grande como su diámetro, a efectos de
minimizar el gradiente de voltaje sobre su superficie. No obstante,
con ciertas configuraciones del manguito de aislamiento y del
electrodo activo, el gradiente de voltaje puede ser suficientemente
grande para permitir la formación de una bolsa de vapor solamente
sobre la parte de la zona de tratamiento expuesta más próxima a la
superficie de contacto del fluido, dejando el extremo distal de la
zona de tratamiento expuesta en contacto con el fluido de
conducción. De este modo se establece el gradiente de voltaje dentro
del fluido de conducción, en el que el borde de la bolsa de vapor
corta la superficie de la parte o zona (34A) de tratamiento del
electrodo activo. El comportamiento eléctrico de dicha parte de
tratamiento del electrodo activo parcialmente rodeado o envuelto es
muy distinto del de una zona de tratamiento completamente envuelta.
La transición de impedancia desde el estado húmedo al estado de
envolvente de vapor es mucho menos acusada que lo que se ha descrito
anteriormente con referencia a la figura 4. En términos de control
de la salida del generador por detección del voltaje máximo o pico,
el comportamiento del conjunto del electrodo ya no es biestable. No
obstante, la demanda de potencia es considerablemente más alta como
resultado del voltaje de vaporización presentado a través de la zona
húmeda de baja impedancia de la zona de tratamiento del electrodo
activo. El efecto clínico no es solamente la vaporización requerida,
sino también un perjudicial efecto térmico que resulta de la
disipación incrementada de potencia.
La disposición envolvente parcial de la zona de
tratamiento del electrodo activo se puede evitar fundamentalmente al
asegurar que la proporción de la longitud de la trayectoria de
conducción entre el punto más alejado de la parte de tratamiento del
electrodo activo y la longitud de la trayectoria de conducción más
corta entre la parte de tratamiento del electrodo activo y la
superficie de contacto del fluido es menor o igual a 2:1, es decir
b/(a+c) \leq 2.
En algunas circunstancias, se puede observar que
la longitud de la trayectoria de conducción entre los electrodos
activo y de retorno es demasiado grande para permitir la
vaporización del fluido conductivo debido a la consiguiente
impedancia en serie grande representada por el fluido. Una caída de
voltaje excesiva puede tener como resultado que se alcance un umbral
de voltaje predeterminado antes de poder conseguir la vaporización.
Preferentemente en este caso, la proporción de la longitud de
trayectoria de conducción más grande con respecto a la longitud
periférica anular de la superficie de contacto del fluido con el
electrodo de retorno no es superior a 1,43:1. En el caso de una
superficie de contacto cilíndrica con el fluido que es coaxial con
el electrodo activo, la proporción de la longitud de trayectoria de
conducción mayor con respecto al diámetro de la superficie de
contacto del fluido es menor o igual a 4,5 : 1. Así pues, con
referencia a la figura 8, b/d \leq 4,5.
El uso primario de la unidad de electrodo
mostrada en la figura 8 es para el corte de tejidos, teniendo por lo
menos una parte de la zona (34A) de tratamiento del electrodo activo
enterrada o embebida en los tejidos a tratar y con el generador
funcionando en la parte de vaporización según las características de
impedancia/potencia mostradas en la figura 4.
Entre las configuraciones alternativas de los
electrodos activos se incluyen la formación de la parte de
tratamiento expuesta (34A) en forma de un gancho, tal como se ha
mostrado en la figura 9. En este caso, el manguito de aislamiento es
cónico, reduciéndose su sección desde la superficie de contacto con
el fluido del electrodo de retorno (38) hacia la cara (36A) del
extremo distal.
Otra alternativa mostrada en la figura 10 tiene
una zona (34a) de tratamiento del electrodo activo en
forma de un gancho en forma de bucle.
forma de un gancho en forma de bucle.
En las realizaciones de las figuras 8, 9 y 10 se
puede apreciar que las dimensiones a, b, c, d son tales que
quedan dentro de los límites de proporciones que se han descrito
anteriormente. Además, en cada caso, el conjunto del electrodo puede
ser considerado como dotado de un eje de tratamiento (42), siendo el
eje a lo largo del cual se puede introducir el instrumento hacia los
tejidos, disponiéndose en retroceso el electrodo de retorno (38) en
la dirección del eje de tratamiento desde el electrodo activo (34A).
Con la finalidad de comparar las diferentes longitudes de
trayectorias de conducción entre el electrodo de retorno y
diferentes partes de la parte de tratamiento del electrodo activo,
se deben considerar trayectorias en un plano común, cuyo plano
contiene el eje de tratamiento (42). En el caso de las vistas de las
figuras 8, 9 y 10, las longitudes de trayectorias mostradas son,
desde luego, en el plano del papel que soporta los dibujos.
Claims (8)
1. Instrumento electroquirúrgico para el secado
de tejidos (80) en presencia de un medio fluido eléctricamente
conductor (78), comprendiendo el instrumento un cuerpo (12), un
vástago alargado (30) y, en un extremo distal del vástago, un
conjunto de electrodo (32), de manera que el conjunto del electrodo
comprende:
- un único electrodo activo (34) que tiene una parte de tratamiento de tejidos expuesta (34A),
- un electrodo de retorno (38) separado de la parte de tratamiento de tejidos por un elemento de aislamiento (36), poseyendo el electrodo de retorno una superficie de contacto de fluido retrasada en dirección longitudinal del instrumento desde la parte de tratamiento del electrodo activo y desde el extremo distal del elemento de aislamiento, siendo el conjunto del electrodo tal que cuando la parte de tratamiento de los tejidos se lleva a una posición adyacente a una superficie de tejidos sumergida en el medio fluido, la superficie de contacto con el fluido se encuentra separada con respecto a la superficie del tejido y el medio fluido completa una trayectoria de conducción entre el electrodo activo y el electrodo de retorno;
de manera que la longitud de la trayectoria de
conducción más corta a través del medio fluido entre la superficie
de contacto del fluido del electrodo de retorno y la parte expuesta
del electrodo activo es como mínimo de 1mm; y
la proporción del área de la superficie del
electrodo de retorno con respecto al área de la superficie del
electrodo activo se encuentra en una gama comprendida desde 5:1 a
40:1.
2. Instrumento, según la reivindicación 1, en el
que la separación longitudinal desde el electrodo de retorno a la
parte de tratamiento de tejidos expuesta del electrodo activo está
comprendida entre 1 mm y 5mm.
3. Instrumento, según la reivindicación 1 ó 2, en
el que el electrodo de retorno comprende un manguito conductor
situado alrededor del elemento de aislamiento detrás de la parte de
tratamiento del electrodo activo.
4. Instrumento, según la reivindicación 1 ó 2, en
el que la parte de tratamiento del electrodo activo está situada en
una parte distal extrema del conjunto, y la superficie de contacto
con el fluido del electrodo de retorno está separada en la parte
próxima con respecto a la parte de tratamiento del electrodo activo,
y en el que la parte expuesta del electrodo activo tiene una
longitud y una anchura, siendo la longitud superior a como mínimo la
mitad de la anchu-
ra.
ra.
5. Instrumento, según cualquiera de las
reivindicaciones 1 a 4, en el que la proporción de (i) la distancia
longitudinal entre el extremo distal de la parte expuesta del
electrodo activo y la parte más alejada del electrodo de retorno, a
(ii) la distancia longitudinal más corta entre la parte expuesta del
electrodo activo y la parte más alejada del electrodo de retorno, es
menor o igual a 2:1.
6. Instrumento, según cualquiera de las
reivindicaciones 1 a 5, en el que el electrodo de retorno tiene una
superficie de contacto con el fluido que rodea el elemento de
aislamiento y en el que la proporción de (i) la distancia
longitudinal entre el extremo distal de la parte expuesta del
electrodo activo y el borde distal de la superficie de contacto con
el fluido del electrodo de retorno a (ii) la circunferencia de la
superficie de contacto del fluido en la zona de su borde distal es
menor o igual a 1,43:1.
7. Instrumento, según cualquiera de las
reivindicaciones 1 a 6, en el que el eje del instrumento comprende
un tubo metálico como elemento estructural principal, y el electrodo
de retorno es la parte extrema distal formada de manera integral
del
tubo.
tubo.
8. Instrumento, según cualquiera de las
reivindicaciones 1 a 7, en el que la separación longitudinal de la
parte de tratamiento expuesta de los tejidos del electrodo activo y
la superficie de contacto con el fluido del electrodo de retorno es
como mínimo de
1 mm.
1 mm.
Applications Claiming Priority (8)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GBGB9512888.0A GB9512888D0 (en) | 1995-06-23 | 1995-06-23 | An electrosurgical generator |
GBGB9512889.8A GB9512889D0 (en) | 1995-06-23 | 1995-06-23 | An electrosurgical instrument |
GB9512889 | 1995-06-23 | ||
GB9512888 | 1995-06-23 | ||
GBGB9600355.3A GB9600355D0 (en) | 1995-06-23 | 1996-01-09 | Electrosurgical instrument |
GB9600355 | 1996-01-09 | ||
GBGB9600352.0A GB9600352D0 (en) | 1996-01-09 | 1996-01-09 | Electrosurgical instrument |
GB9600352 | 1996-01-09 |
Publications (1)
Publication Number | Publication Date |
---|---|
ES2233239T3 true ES2233239T3 (es) | 2005-06-16 |
Family
ID=27451303
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
ES00110410T Expired - Lifetime ES2233239T3 (es) | 1995-06-23 | 1996-06-20 | Instrumento electroquirurgico. |
ES96918768T Expired - Lifetime ES2150676T5 (es) | 1995-06-23 | 1996-06-20 | Instrumento electroquirurgico. |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
ES96918768T Expired - Lifetime ES2150676T5 (es) | 1995-06-23 | 1996-06-20 | Instrumento electroquirurgico. |
Country Status (13)
Country | Link |
---|---|
US (2) | US6004319A (es) |
EP (2) | EP0771176B2 (es) |
JP (1) | JP3798022B2 (es) |
KR (1) | KR100463935B1 (es) |
CN (1) | CN1095641C (es) |
AR (1) | AR002570A1 (es) |
AU (1) | AU710619B2 (es) |
BR (1) | BR9609421A (es) |
CA (1) | CA2224858C (es) |
DE (2) | DE69609473T3 (es) |
ES (2) | ES2233239T3 (es) |
IL (1) | IL122713A (es) |
WO (1) | WO1997000647A1 (es) |
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-
1996
- 1996-06-20 ES ES00110410T patent/ES2233239T3/es not_active Expired - Lifetime
- 1996-06-20 CA CA002224858A patent/CA2224858C/en not_active Expired - Lifetime
- 1996-06-20 EP EP96918768A patent/EP0771176B2/en not_active Expired - Lifetime
- 1996-06-20 US US08/702,512 patent/US6004319A/en not_active Expired - Lifetime
- 1996-06-20 EP EP00110410A patent/EP1025807B1/en not_active Expired - Lifetime
- 1996-06-20 WO PCT/GB1996/001473 patent/WO1997000647A1/en active IP Right Grant
- 1996-06-20 AU AU61321/96A patent/AU710619B2/en not_active Expired
- 1996-06-20 CN CN96196280A patent/CN1095641C/zh not_active Expired - Lifetime
- 1996-06-20 ES ES96918768T patent/ES2150676T5/es not_active Expired - Lifetime
- 1996-06-20 DE DE69609473T patent/DE69609473T3/de not_active Expired - Lifetime
- 1996-06-20 DE DE69634014T patent/DE69634014T2/de not_active Expired - Lifetime
- 1996-06-20 BR BR9609421A patent/BR9609421A/pt not_active IP Right Cessation
- 1996-06-20 IL IL12271396A patent/IL122713A/en not_active IP Right Cessation
- 1996-06-20 JP JP50366497A patent/JP3798022B2/ja not_active Expired - Lifetime
- 1996-06-20 KR KR1019970709680A patent/KR100463935B1/ko not_active IP Right Cessation
- 1996-06-21 AR ARP960103276A patent/AR002570A1/es unknown
-
1998
- 1998-03-27 US US09/049,728 patent/US6056746A/en not_active Expired - Lifetime
Also Published As
Publication number | Publication date |
---|---|
AU710619B2 (en) | 1999-09-23 |
AU6132196A (en) | 1997-01-22 |
AR002570A1 (es) | 1998-03-25 |
DE69609473D1 (de) | 2000-08-31 |
DE69609473T3 (de) | 2006-09-28 |
EP1025807A2 (en) | 2000-08-09 |
EP0771176A1 (en) | 1997-05-07 |
EP1025807A3 (en) | 2000-10-04 |
ES2150676T3 (es) | 2000-12-01 |
IL122713A (en) | 2001-04-30 |
MX9800249A (es) | 1998-07-31 |
JPH11507857A (ja) | 1999-07-13 |
BR9609421A (pt) | 1999-05-18 |
EP0771176B1 (en) | 2000-07-26 |
EP0771176B2 (en) | 2006-01-04 |
KR100463935B1 (ko) | 2005-05-16 |
CN1193268A (zh) | 1998-09-16 |
JP3798022B2 (ja) | 2006-07-19 |
KR19990028364A (ko) | 1999-04-15 |
US6056746A (en) | 2000-05-02 |
DE69634014T2 (de) | 2006-03-02 |
IL122713A0 (en) | 1998-08-16 |
EP1025807B1 (en) | 2004-12-08 |
CA2224858A1 (en) | 1997-01-09 |
DE69634014D1 (de) | 2005-01-13 |
US6004319A (en) | 1999-12-21 |
CA2224858C (en) | 2006-11-14 |
CN1095641C (zh) | 2002-12-11 |
WO1997000647A1 (en) | 1997-01-09 |
DE69609473T2 (de) | 2001-04-26 |
ES2150676T5 (es) | 2006-04-16 |
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