BR112012033478B1 - Dispositivo médico - Google Patents
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Abstract
DISPOSITIVO MÉDICO. A presente invenção refere-se a um dispositivo que tem um cabo e um efetor de extremidade acoplado ao cabo. O efetor de extremidade tem ao menos um eletrodo para fornecer sinais elétricos a um tecido ou a um vaso a ser tratado. É fornecido um circuito de acionamento de RF que é aplicado ao eletrodo do efetor de extremidade. O circuito de acionamento e RF contém um circuito ressonante e um controlador de frequência que é usado para variar a frequência de um sinal passado através do circuito ressonante para controlar a potência fornecida ao eletrodo do efetor de extremidade.
Description
[0001] A presente invenção refere-se ao campo de dispositivos médicos e, em particular, embora não exclusivamente, a dispositivos médicos de cauterização e de corte. A invenção se refere também a circuitos de acionamento e a métodos de acionar tais dispositivos médicos.
[0002] Muitos procedimentos cirúrgicos exigem o corte ou a ligação de vasos sanguíneos ou de outro tecido interno. Muitos procedimentos cirúrgicos são executados com o uso de técnicas minimamente invasivas, nos quais um dispositivo de mão de cauterização é usado pelo cirurgião para executar o corte ou a ligação. O dispositivo de mão de cauterização existente exige uma fonte de alimentação na área de trabalho e componentes eletrônicos de controle que são conectados ao dispositivo através de uma linha de alimentação elétrica. A figura 10 ilustra tal dispositivo de mão de cauterização existente utilizado atualmente.
[0003] Sabe-se de longa data que os dispositivos existentes são pouco práticos e difíceis de utilizar durante uma operação cirúrgica devido ao grande tamanho da fonte de alimentação e dos componentes eletrônicos de controle, e devido à conexão do dispositivo de mão de cauterização à fonte de alimentação e aos componentes eletrônicos de controle. Sabe-se, também, de longa data, que esses problemas poderiam ser superados fornecendo-se um dispositivo de mão de cauterização alimentado por bateria no qual a fonte de alimentação e os componentes eletrônicos de controle são montados dentro do próprio dispositivo, como no interior do cabo do dispositivo. Entretanto, não se trata simplesmente de "miniaturizar" os componentes eletrônicos. A energia fornecida ao dispositivo durante o procedimento cirúrgico e o design atual dos componentes eletrônicos são tais que são necessários grandes capacitores, indutores e transformadores, além de dissipadores de calor e ventiladores. A figura 11 ilustra em mais detalhes as diferentes partes da fonte de alimentação e dos componentes eletrônicos de controle que são usados no modelo existente. Embora seja possível reduzir o tamanho dos componentes eletrônicos de detecção e de controle, outras partes do circuito não podem ser miniaturizadas dessa maneira.
[0004] Em particular, os componentes eletrônicos com o design existente utilizam um circuito para fornecer uma fonte de alimentação ajustável de 24 volts; FETs (transistores de efeito de campo) e circuito de acionamento associado; um transformador para aumentar a tensão de alimentação; e um circuito de filtração para remover os harmônicos dos níveis de tensão de onda quadrada que são gerados pelas chaves de FET e pelo transformador. Dado os níveis de tensão e os níveis de energia usados para acionar o dispositivo de cauterização, os transformadores e os filtros de saída precisam ser todos dispositivos relativamente volumosos, sendo necessários grandes dissipadores de calor e um ventilador para resfriar as chaves de FET.
[0005] A presente invenção visa fornecer um design de circuito alternativo que permitirá a miniaturização do circuito de modo que o circuito possa ser construído no interior do dispositivo de mão de cauterização, e ao mesmo tempo capaz de fornecer a energia e o controle necessários para o procedimento médico.
[0006] A presente invenção apresenta um dispositivo médico que compreende um efetor de extremidade tendo ao menos um contato elétrico, um circuito gerador de radiofrequência (RF) para gerar um sinal de acionamento de RF e fornecer o sinal de acionamento de RF ao pelo menos um contato elétrico, e sendo que o circuito gerador de RF compreende um circuito ressonante. Em uma modalidade, o circuito gerador de radiofrequência compreende um circuito de chaveamento que gera um sinal cíclico, por exemplo, um sinal de onda quadrada, de uma fonte CC e sendo que o circuito ressonante é configurado para receber o sinal cíclico do circuito de chaveamento. A fonte CC é, de preferência, fornecida por uma ou mais baterias que podem ser montadas em um compartimento (como um cabo) do dispositivo.
[0007] De acordo com outro aspecto, a invenção apresenta um dispositivo médico que compreende: um cabo para preensão pelo usuário; um efetor de extremidade acoplado ao cabo, sendo que o efetor de extremidade tem ao menos um contato elétrico; terminais de bateria para conexão a uma ou mais baterias; um circuito gerador de radiofrequência (RF) acoplado aos ditos terminais de bateria e com a capacidade de gerar um sinal de acionamento de RF e fornecer o sinal de acionamento de RF ao pelo menos um contato elétrico do dito efetor de extremidade; sendo que o circuito gerador de radiofrequência compreende: um circuito de chaveamento para gerar um sinal cíclico (que pode ser um sinal de onda quadrada modulado por largura de pulso) a partir de uma diferença de potencial entre os ditos terminais de bateria; e um circuito de acionamento ressonante acoplado ao dito circuito de chaveamento e operável para filtrar o sinal cíclico gerado pelo circuito de chaveamento; e sendo que o sinal de acionamento de RF é obtido com o uso de um sinal de saída do dito circuito ressonante.
[0008] O dispositivo médico pode compreender também um circuito de controle (que pode compreender hardware e/ou software) que varia a frequência do sinal de acionamento de RF. O circuito de controle pode variar a frequência com base em uma medição do sinal de acionamento de RF para controlar ao menos um parâmetro dentre potência, tensão e/ou corrente fornecido ao pelo menos um contato elétrico do efetor de extremidade. Em uma modalidade preferencial, a medição é obtida a partir de um circuito de amostragem que opera de maneira síncrona em relação à frequência do sinal de acionamento de RF. A frequência na qual o circuito de amostragem faz a amostragem do sinal detectado pode ser uma fração inteira da frequência do sinal de acionamento de RF.
[0009] Em uma modalidade, o circuito de controle varia a frequência do sinal de acionamento de RF em torno (de preferência logo acima ou logo abaixo) da frequência de ressonância do circuito ressonante. A característica de ressonância do circuito ressonante pode variar com uma carga conectada ao pelo menos um contato elétrico e o circuito de controle pode ser configurado para variar a frequência de RF de acionamento para rastrear alterações na característica de ressonância do circuito ressonante.
[00010] De acordo com outro aspecto, a invenção apresenta um dispositivo médico que compreende: um cabo para preensão pelo usuário; um efetor de extremidade acoplado ao cabo e tendo ao menos um contato elétrico; um circuito gerador de radiofrequência (RF) com a capacidade de gerar um sinal de acionamento de RF e de fornecer o sinal de acionamento de RF ao pelo menos um contato elétrico; e um circuito de controle operável para variar a frequência do sinal de acionamento de RF para controlar ao menos um parâmetro dentre potência, tensão e corrente fornecido ao pelo menos um contato do efetor de extremidade.
[00011] O circuito gerador de RF pode compreender um gerador de sinal que gera um sinal cíclico na frequência de RF; e um atenuador dependente da frequência, que atenua o sinal cíclico de acordo com a frequência do sinal cíclico. O atenuador dependente de frequência pode ser um atenuador sem perdas e pode compreender um circuito ressonante que tem uma frequência de ressonância igual ou próxima da frequência de RF do sinal cíclico.
[00012] A presente invenção fornece também um dispositivo médico que compreende: um cabo para preensão pelo usuário; um efetor de extremidade acoplado ao cabo e tendo ao menos um contato elétrico; um circuito gerador de radiofrequência (RF) com a capacidade de gerar um sinal de acionamento de RF e de fornecer o sinal de acionamento de RF ao pelo menos um contato elétrico; uma entrada para receber um sinal detectado que varia com o sinal de acionamento de RF aplicado ao pelo menos um contato elétrico; um circuito de amostragem para fazer a amostragem do sinal detectado na dita entrada; um circuito de medição operável para fazer medições do sinal de acionamento de RF com o uso de amostras obtidas do circuito de amostragem; e um circuito de controle operável para controlar o circuito gerador de RF que depende das medições feitas pelo circuito de medição, para variar a frequência do sinal de acionamento de RF gerado; sendo que o circuito de amostragem faz a amostragem do sinal detectado a uma frequência de amostragem que varia em sincronismo com a frequência do sinal de acionamento de RF.
[00013] A invenção fornece também um método para operação de um dispositivo médico que compreende a geração de um sinal de RF e a aplicação do sinal de RF a ao menos um eletrodo de um efetor de extremidade do dispositivo médico, e o controle da frequência do sinal de RF gerado para controlar ao menos um parâmetro dentre potência, corrente e tensão aplicado a ao menos um eletrodo.
[00014] De acordo com outro aspecto, a invenção apresenta um método de cauterização de um vaso ou tecido, sendo que o método compreende: prender o vaso ou tecido com um efetor de extremidade de um dispositivo médico; aplicar um sinal de RF a ao menos um eletrodo do efetor de extremidade que está em contato com o vaso ou tecido; e controlar a frequência do sinal de RF para controlar ao menos um parâmetro dentre potência, corrente e tensão aplicado ao tecido para executar a cauterização.
[00015] Os métodos acima podem usar o dispositivo médico descrito anteriormente, embora isso não seja essencial.
[00016] A etapa de controle pode variar a frequência do sinal de RF para controlar a potência aplicada ao tecido ou vaso, e o método pode compreender adicionalmente obter medições da impedância do tecido ou vaso e variar a potência desejada aplicada ao tecido ou vaso em dependência das medições da impedância obtidas.
[00017] Essas e várias outras características e aspectos da invenção ficarão aparentes a partir da seguinte descrição detalhada das modalidades descritas com referência às figuras em anexo nas quais: a figura 1 ilustra um dispositivo de mão de cauterização que tem baterias e os circuitos de acionamento e de controle montados em uma porção de cabo do dispositivo; a figura 2 é um diagrama em parte de blocos, em parte esquemático que ilustra os principais componentes do circuito de RF de acionamento e o circuito de controle usados em uma modalidade da invenção; a figura 3 é um diagrama de blocos que ilustra os principais componentes de um controlador usado para controlar a operação do circuito de RF de acionamento mostrado na figura 2; a figura 4 é um diagrama de sincronização que ilustra os sinais de RF de acionamento aplicados ao dispositivo de cauterização e que ilustra uma maneira na qual as amostras sincronizadas podem ser obtidas para medir os sinais de acionamento; a figura 5a é um gráfico que ilustra os limites que são impostos sobre a tensão e a corrente fornecida ao dispositivo de cauterização mostrado na figura 1; a figura 5b ilustra um gráfico de potência resultante obtido mediante a combinação das plotagens de corrente e tensão mostradas na figura 5a; a figura 6 é um gráfico que ilustra a maneira na qual as características de ressonância do circuito de RF de acionamento mostrado na figura 2 variam com cargas diferentes; a figura 7 é um fluxograma que ilustra a operação de um algoritmo de controle de frequência usado para controlar a frequência dos sinais de RF de acionamento aplicados ao dispositivo de cauterização; a figura 8 é um gráfico que ilustra uma maneira na qual o limite de potência pode ser variado pelos componentes eletrônicos de controle durante um procedimento cirúrgico; a figura 9 é um diagrama em parte de blocos, em parte esquemático que ilustra os principais componentes de um outro circuito de RF de acionamento e de controle das modalidades da invenção; a figura 10 ilustra a forma de um dispositivo de mão de cauterização da técnica anterior que é conectado à fonte de alimentação e aos componentes eletrônicos de controle através de uma linha de alimentação de energia; e a figura 11 é uma vista em planta que ilustra os diferentes componentes dos componentes eletrônicos existentes usados para acionar e controlar o dispositivo de mão de cauterização mostrado na figura 10.
[00018] Muitos procedimentos cirúrgicos exigem o corte ou a ligação de vasos sanguíneos ou de outro tecido vascular. Com procedimentos cirúrgicos minimamente invasivos, os cirurgiões executam operações cirúrgicas através de uma pequena incisão no corpo do paciente. Devido à limitação de espaço, os cirurgiões com frequência têm dificuldade em controlar o sangramento pinçando e/ou amarrando vasos sanguíneos cortados transversalmente. Utilizando um fórceps eletrocirúrgico, um cirurgião pode cauterizar, coagular/dessecar e/ou simplesmente reduzir ou retardar o sangramento mediante o controle da energia eletrocirúrgica aplicada através dos elementos de garra do fórceps eletrocirúrgico.
[00019] A figura 1 ilustra a forma de um dispositivo médico eletrocirúrgico 1 que é projetado para procedimentos médicos minimamente invasivos, De acordo com uma modalidade da presente invenção. Conforme mostrado, o dispositivo 1 é um dispositivo autocontido que tem uma haste alongada 3 com um cabo 5 conectado na extremidade proximal da haste 3 e um efetor de extremidade 7 conectado na extremidade distal da haste 3. Nessa modalidade, o efetor de extremidade 7 compreende o fórceps médico 9 e uma lâmina de corte (não mostrada) que são controlados pelo usuário pela manipulação das alavancas de controle 11 e 13 do cabo 5.
[00020] Durante um procedimento cirúrgico, a haste 3 é inserida através de um trocarte para ganhar acesso ao interior do paciente e ao local de operação. O cirurgião manipula o fórceps 9 com o uso do cabo 5 e das alavancas de controle 11 e 13 até que o fórceps 9 esteja localizado ao redor do vaso a ser cauterizado. A energia elétrica a uma frequência de RF (descobriu-se que frequências acima de cerca de 50 kHz não afetam o sistema nervoso humano) é então aplicada, de maneira controlada, ao fórceps 9 para executar a cauterização desejada. Conforme mostrado na figura 1, nessa modalidade, o cabo 5 acomoda baterias 15 e componentes eletrônicos de controle 17 para gerar e controlar a energia elétrica necessária para executar a cauterização. Dessa maneira, o dispositivo 1 é autocontido no sentido de que o mesmo não necessita de um quadro de controle e um fio de alimentação separados para fornecer a energia elétrica ao fórceps 9.
[00021] A figura 2 é um diagrama em parte esquemático, em parte de blocos que ilustra o circuito de RF de acionamento e de controle 20 usado nessa modalidade para gerar e controlar a energia elétrica de RF fornecida ao fórceps 9. Conforme será explicado em mais detalhes a seguir, nessa modalidade, o circuito de acionamento 20 é um circuito baseado em ressonância e o circuito de controle opera para controlar a frequência de operação do sinal de acionamento de modo que o mesmo seja variado em torno da frequência de ressonância do circuito de acionamento, que, por sua vez, controla a quantidade de energia fornecida ao fórceps 9. A maneira como isso é conseguido ficará aparente com a descrição a seguir.
[00022] Conforme mostrado na figura 2, o circuito de acionamento 20 compreende as baterias 15 descritas anteriormente, que são configuradas para fornecer, neste exemplo, fontes de tensão de 0 V e 24 V. Um capacitor de entrada (Cen) 21 é conectado entre as fontes de tensão de 0 V e de 24 V para fornecer uma baixa impedância de fonte. Um par de chaves de FET 23-1 e 23-2 (que nessa modalidade são ambas de canal N para reduzir as perdas de energia) é conectado em série entre a fonte de tensão de 0 V e a fonte de tensão de 24 V. É fornecido um circuito de acionamento de terminal FET 25 que gera dois sinais de acionamento - um para acionar cada um dos dois FETs 23. O circuito de acionamento de terminal FET 25 gera sinais de acionamento que fazem com que o FET superior (23-1) seja ligado quando o FET inferior (23-2) está desligado e vice-versa. Isso faz com que o nó 27 seja conectado alternadamente à fonte de tensão de 24 V (quando o FET 23-1 é ligado) e à fonte de tensão de 0 V (quando o FET 23-2 é ligado). A figura 2 mostra, também, os diodos parasíticos internos 28-1 e 28-2 dos FETs 23 correspondentes, que transmitem energia durante quaisquer períodos em que os FETs 23 estão abertos.
[00023] Conforme mostrado na figura 2, o nó 27 é conectado a um circuito ressonante capacitor-indutor-indutor 28 formado pelo capacitor Cs 29, o indutor Ls 31 e o indutor Lm 33. O circuito de acionamento de terminal FET 25 é configurado para gerar sinais de acionamento a uma frequência de acionamento (fd) que abre e fecha as chaves de FET 23 em torno da frequência de ressonância do circuito ressonante 28. Como um resultado da característica de ressonância do circuito ressonante 28, a tensão de onda quadrada no nó 27 fará com que uma corrente substancialmente senoidal à frequência de acionamento (fd) flua pelo circuito ressonante 28. Conforme mostrado na figura 2, o indutor Lm 33 é o primário de um transformador 35, cujo secundário é formado pelo indutor Lsec 37. O transformador 35 converte a tensão de acionamento (Vd) no indutor Lm 33 para a tensão de carga (VL) que é aplicada à carga (representada pela resistência de carga Rcarga 39 na figura 2) que corresponde à impedância das garras do fórceps e qualquer tecido ou vaso seguro pelo fórceps 9. Conforme mostrado na figura 2, é fornecido um par de capacitores de bloqueio de CC Cbl 40-1 e 40-2 para evitar a aplicação de qualquer sinal de CC à carga 39.
[00024] Nessa modalidade, a quantidade de energia elétrica fornecida ao fórceps 9 é controlada pela variação da frequência dos sinais de chaveamento usados para comutar os FETs 23. Isso funciona porque o circuito ressonante 28 age como um atenuador dependente da frequência (sem perdas). Quanto mais próximo o sinal de acionamento estiver da frequência de ressonância do circuito ressonante 28, menos atenuado será o sinal de acionamento. De modo similar, à medida que a frequência do sinal de acionamento se afasta da frequência de ressonância do circuito 28, maior a atenuação do sinal de acionamento e, portanto, menor a energia fornecida à carga. Nessa modalidade, a frequência dos sinais de chaveamento gerados pelo circuito de acionamento de terminal FET 25 é controlada por um controlador 41 com base em uma potência desejada a ser fornecida à carga 39 e as medições da tensão de carga (VL) e da corrente de carga (iL) obtidas por um circuito de detecção de tensão 43 e um circuito de detecção de corrente 45 convencionais. A maneira como o controlador 41 opera será descrita em mais detalhes a seguir.
[00025] A figura 3 é um diagrama de blocos que ilustra os principais componentes do controlador 41. Nessa modalidade, o controlador 41 é um controlador baseado em microprocessador e, portanto, a maioria dos componentes mostrados na figura 3 é formada por componentes baseados em software. Entretanto, em vez disso, pode ser utilizado um controlador baseado em hardware 41. Conforme mostrado, o controlador 41 inclui um circuito de amostragem 51 sincronizado I,Q que recebe os sinais detectados de tensão e de corrente enviados pelos circuitos de detecção 43 e 45 e obtém amostras correspondentes que são passadas para um módulo de cálculo 53 de potência, tensão Vrms e corrente Irms. O módulo de cálculo 53 usa amostras recebidas para calcular a tensão RMS e a corrente RMS aplicadas à carga 39 (fórceps 9 e tecido/vaso seguro pelo mesmo) e a partir delas a potência que está sendo fornecida à carga 39. Os valores determinados são então passados para um módulo de controle de frequência 55 e para um módulo de controle do dispositivo médico 57. O módulo de controle do dispositivo médico 57 usa os valores para determinar a impedância atual da carga 39 e com base nessa impedância calculada e em um algoritmo predefinido, determina qual potência de ponto de ajuste (Paju) deve ser aplicada ao módulo de controle de frequência 55. O módulo de controle do dispositivo médico 57 é, por sua vez, controlado pelos sinais recebidos de um módulo de entrada de dados pelo usuário 59 que recebe dados do usuário (por exemplo, acionamento de botões ou ativação das alavancas de controle 11 ou 13 no cabo 5) e controla também dispositivos de saída (luzes, um monitor, alto-falante, ou similares) no cabo 5 via um módulo de saída do usuário 61.
[00026] O módulo de controle de frequência 55 usa os valores obtidos do módulo de cálculo 53, do ponto de ajuste de potência (Paju) obtido do módulo de controle do dispositivo médico 57 e dos limites predefinidos do sistema (a ser explicado mais adiante), para determinar se a frequência aplicada deve ou não ser aumentada ou diminuída. O resultado dessa decisão é então enviado para um módulo de geração de onda quadrada 63 que, nessa modalidade, aumenta ou diminui em incrementos ou decrementos de 1 kHz a frequência de um sinal de onda quadrada gerado pelo módulo, dependendo da decisão recebida. Conforme será compreendido pelos versados na técnica, em uma modalidade alternativa, o módulo de controle de frequência 55 pode determinar não apenas se a frequência deve ser aumentada ou diminuída, mas também a quantidade de alteração de frequência necessária. Nesse caso, o módulo de geração de onda quadrada 63 geraria o sinal de onda quadrada correspondente com a mudança desejada de frequência. Nessa modalidade, o sinal de onda quadrada gerado pelo módulo de geração de onda quadrada 63 é enviado para o circuito de acionamento de terminal FET 25, que amplifica o sinal e, então, o aplica ao FET 23-1. O circuito de acionamento de terminal FET 25 também inverte o sinal aplicado ao FET 23-1 e aplica o sinal invertido ao FET 23-2. Sinais de acionamento e medições dos sinais
[00027] A figura 4 é um gráfico de sinais que mostra os sinais de chaveamento aplicados aos FETs 23; um sinal senoidal representando a corrente ou tensão medida aplicada à carga 39; e as sincronizações quando o circuito sincronizado de amostragem 51 faz a amostragem da tensão de carga e da corrente de carga detectadas. Em particular, a figura 4 mostra o sinal de chaveamento (designado PWM1H) aplicado ao FET superior 23-1 e o sinal de chaveamento (designado PWM1L) aplicado ao FET inferior 23-2. Embora não ilustrado por uma questão de simplicidade, existe um tempo morto entre PWM1H e PWM1L para assegurar que ambos os FETs 23 não sejam ativados ao mesmo tempo. A figura 4 mostra também a tensão/corrente de carga medida (designada SAÍDA). Tanto a tensão de carga como a corrente de carga serão uma forma de onda senoidal, embora possam estar defasadas, dependendo da impedância da carga 39. Conforme mostrado, a corrente de carga e a tensão de carga estão na mesma frequência de acionamento (fd) que os sinais de chaveamento (PWM1H e PWM1L) usados para comutar os FETs 23. Normalmente, durante a amostragem de um sinal senoidal, é necessário fazer a amostragem do sinal a uma taxa que corresponde a ao menos duas vezes a frequência do sinal cuja amostragem está sendo feita - isto é, duas amostras por período. Entretanto, como o controlador 41 conhece a frequência dos sinais de chaveamento, o circuito sincronizado de amostragem 51 pode fazer a amostragem do sinal de tensão/corrente medido a uma taxa mais baixa. Nessa modalidade, o circuito sincronizado de amostragem 51 faz a amostragem do sinal medido uma vez por período, mas em fases diferentes em períodos adjacentes. Na figura 4, isto é ilustrado pelas amostras "I" e "Q". O tempo no qual o circuito sincronizado de amostragem 51 faz essas amostragens é controlado, nessa modalidade, pelos dois sinais de controle PWM2 e PWM3, que têm uma fase fixa em relação aos sinais de chaveamento (PWM1H e PWM1L) e são defasados entre si (de preferência por um quarto do período para facilitar os cálculos subsequentes). Conforme mostrado, o circuito sincronizado de amostragem 51 obtém uma amostra "I" em cada segunda borda de subida do sinal PWM2 e o circuito sincronizado de amostragem 51 obtém uma amostra "Q" em cada segunda borda de subida do sinal PWM3. O circuito sincronizado de amostragem 51 gera os sinais de controle PWM2 e PWM3 a partir do sinal de onda quadrada gerado pelo gerador de onda quadrada 63 (que está na mesma frequência que os sinais de chaveamento PWM1H e PWM1L). Dessa forma, quando a frequência dos sinais de chaveamento é alterada, a frequência dos sinais de controle de amostragem PWM2 e PWM3 também muda (embora suas fases relativas permaneçam as mesmas). Dessa maneira, o circuito de amostragem 51 muda continuamente a sincronização na qual faz a amostragem dos sinais detectados de tensão e de corrente à medida que a frequência do sinal de acionamento é variada, de modo que as amostras são sempre tomadas nos mesmos pontos no tempo dentro do período do sinal de acionamento. Portanto, o circuito de amostragem 51 realiza uma operação de amostragem "sincronizada" em vez de uma operação de amostragem mais convencional que faz a amostragem apenas do sinal de entrada a uma taxa fixa de amostragem definida por um sinal regulador fixo de amostragem.
[00028] As amostras obtidas pelo circuito sincronizado de amostragem 51 são então passadas para o módulo de cálculo 53 de potência, tensão Vrms e corrente Irms que pode determinar a magnitude e a fase do sinal medido a partir apenas de uma amostra "I" e uma amostra "Q" da corrente de carga e da tensão de carga. Entretanto, nessa modalidade, para obter uma média, o módulo de cálculo 53 calcula a média de amostras "I" consecutivas para fornecer um valor médio de "I" e de amostras "Q" consecutivas para determinar um valor médio de "Q"; e, então, o módulo usa os valores médios de I e Q para determinar a magnitude e a fase do sinal medido (de maneira convencional). Conforme será compreendido pelos versados na técnica, com uma frequência de acionamento de cerca de 400 kHz e amostragem uma vez por período significa que o circuito sincronizado de amostragem 51 terá uma taxa de amostragem de 400 kHz e o módulo de cálculo 53 produzirá uma medição de tensão e uma medição de corrente a cada 0,01 ms. A operação do circuito sincronizado de amostragem 51 oferece um aprimoramento em relação aos produtos existentes, nos quais as medições não podem ser feitas à mesma taxa e apenas as informações sobre magnitude estão disponíveis (as informações de fase são perdidas).
[00029] Como ocorre com qualquer sistema, existem certos limites que podem ser impostos sobre a potência, a corrente e a tensão que podem ser fornecidas ao fórceps 9. Os limites usados nessa modalidade e a maneira como são controlados serão descritos a seguir.
[00030] Nessa modalidade, o circuito de RF de acionamento 20 é projetado para fornecer ao tecido uma onda senoidal de potência limitada com os seguintes requisitos: 1) Fornecida com uma fonte CC nominal de 24 V 2) Forma de onda de saída substancialmente senoidal a aproximadamente 400 kHz 3) Saída de potência limitada de 45 W 4) Corrente limitada a 1,4 Arms e tensão limitada a 85 Vrms
[00031] Os dois últimos requisitos são representados graficamente nas figuras 5a e 5b. Em particular, a figura 5a ilustra gráficos idealizados de tensão e corrente para cargas entre 1 Ohm e 10 k Ohms em uma escala logarítmica; e a figura 5b ilustra a potência fornecida à carga 39 para cargas entre 1 Ohm e 10 k Ohms.
[00032] O módulo de controle de frequência 55 mantém dados que definem esses limites e os utiliza para controlar a decisão de aumentar ou diminuir a frequência de excitação. Característica de ressonância e controle de frequência
[00033] Conforme mencionado anteriormente, a quantidade de energia elétrica fornecida ao fórceps 9 é controlada pela variação da frequência dos sinais de chaveamento usados para comutar os FETs 23. Isso é feito com usando-se o fato de que a impedância do circuito ressonante 28 varia rapidamente com a frequência. Portanto, variando- se a frequência dos sinais de chaveamento, a magnitude da corrente através do circuito ressonante 28, e portanto através da carga 39, pode ser variada conforme necessário para regular a potência de saída.
[00034] Conforme será compreendido pelos versados na técnica, o circuito ressonante 28 é acoplado a uma carga 39 cuja impedância varia durante o procedimento cirúrgico. De fato, o módulo de controle do dispositivo médico 57 usa essa variação para determinar se o tecido ou vaso foi cauterizado, coagulado/dessecado. A impedância variante da carga 39 muda a frequência característica do circuito de RF de acionamento 20 e, portanto, a corrente que flui através do circuito ressonante 28. Isto é ilustrado na figura 6, que é uma curva 65 que ilustra a maneira na qual a corrente através do circuito ressonante 28 varia com a frequência de acionamento para um valor fixo de impedância da carga. À medida que a impedância da carga 39 aumenta, a característica de ressonância 65 muda de formato (o pico pode aumentar ou diminuir em altura) e se move para a esquerda, e, à medida que a impedância da carga diminui, a característica de ressonância muda seu formato e se move para a direita. Portanto, o módulo de controle de frequência 55 deve operar com rapidez suficiente para rastrear as alterações de característica de ressonância 65. Isso é facilmente conseguido nessa modalidade, onde as medições de potência, corrente e tensão estão disponíveis a cada 0,01 ms. Em termos gerais, as medições serão necessárias apenas a uma taxa de cerca de uma vez a cada 0,1 s para rastrear as alterações. Entretanto, podem ocorrer alterações repentinas na característica de ressonância 65 que o módulo de controle de frequência 55 não pode rastrear. Quando isso acontece, o módulo de controle de frequência 55 reinicializa a frequência de operação a um valor que o módulo sabe que estará em um lado da característica.
[00035] Quando a impedância do circuito ressonante 28 aumenta sensivelmente tanto acima como abaixo da ressonância, é possível operar o circuito de RF de acionamento 20 acima ou abaixo da frequência de ressonância. Nessa modalidade, o módulo de controle de frequência 55 controla a operação do circuito de acionamento 20 de modo que o mesmo opere ligeiramente acima da frequência de ressonância, uma vez que isso deve levar a menores perdas de comutação através dos FETs 23.
[00036] A figura 7 ilustra o processamento realizado nessa modalidade pelo módulo de cálculo 53 e pelo módulo de controle de frequência 55. Conforme mostrado, no início do processo na etapa s1, o módulo de controle 55 ativa o sinal de acionamento de RF na frequência máxima definida do sistema transmitindo um sinal de inicialização para o módulo de geração de onda quadrada 63. Contanto que o módulo de controle 55 não tenha recebido, na etapa s3, um sinal de desativação do módulo de controle do dispositivo médico 57, o processamento continua até a etapa s5 onde o módulo de cálculo 53 obtém as amostras de tensão e de corrente do circuito sincronizado de amostragem 51. Na etapa s7, o módulo de cálculo 53 calcula o quadrado da tensão e o quadrado da corrente e a potência fornecida multiplicando a tensão medida pela corrente medida. Esses valores calculados são então transmitidos para o módulo de controle de frequência 55 que compara, na etapa s9, os valores com os limites definidos para a tensão, corrente e potência aplicadas. Os limites de tensão e corrente são limites estáticos definidos antecipadamente. Contudo, o limite de potência depende do procedimento médico e é definido pelo ponto de ajuste de potência (Paju) fornecido pelo módulo de controle do dispositivo médico 57. Se cada um dos valores medidos estiver abaixo do limite correspondente, então, na etapa s11, o módulo de controle de frequência 55 decidirá diminuir a frequência de acionamento e um comando de diminuição é transmitido ao gerador de onda quadrada 63. No início do processamento, a frequência de acionamento é ajustada para um valor máximo definido (nessa modalidade 500 kHz), que estará sempre acima do pico de ressonância da característica 65, independentemente da impedância da carga. Portanto, independentemente da carga 39, a frequência de operação inicial deve estar no lado direito da curva de ressonância mostrada na figura 6. Com a diminuição da frequência de acionamento, esta se aproximará da frequência de ressonância do circuito ressonante 28. Como um resultado, a corrente aplicada aumentará e mais potência será fornecida para a carga 39. O processamento retorna, então, à etapa s3 e o processo acima é repetido.
[00037] Portanto, a corrente e a potência aplicadas à carga 39 devem aumentar até que um dos limites seja alcançado. Nesse ponto, o módulo de controle 55 determinará, na etapa s9, que foi atingido um limite e, portanto, seguirá para a etapa s13, onde o módulo de controle 55 decide aumentar a frequência de acionamento e envia um comando de aumento ao o módulo de geração de onda quadrada 63. Isso fará com que a frequência de acionamento se distancie da frequência de ressonância do circuito 28 e, portanto, a corrente e a potência fornecidas à carga 39 serão diminuídas. O processamento retorna, então, à etapa s3 como antes.
[00038] Dessa forma, ao iniciar em um lado do pico de ressonância e lentamente mover a frequência de acionamento na direção e afastando-se do pico de ressonância, o nível de corrente e de potência aplicado à carga 39 pode ser controlado dentro dos limites definidos mesmo que a impedância da carga varie e a característica de ressonância 65 do circuito ressonante 28 seja alterada à medida que o tecido/vaso é cauterizado.
[00039] Conforme será compreendido pelos versados na técnica, também seria possível iniciar no lado esquerdo do pico de ressonância e aumentar a frequência de acionamento para aumentar a potência fornecida e diminuir a frequência de acionamento para diminuir a potência fornecida.
[00040] Conforme mencionado anteriormente, o módulo de controle do dispositivo médico 57 controla a operação geral do dispositivo de cauterização 1. Ele recebe dados do usuário através do módulo de entrada de dados pelo usuário 59. Esses dados (entradas) podem especificar que as garras do fórceps 9 estão prendendo um vaso ou tecido e que o usuário deseja iniciar a cauterização. Em resposta, nessa modalidade, o módulo de controle do dispositivo médico 57 inicia um procedimento de controle de cauterização. Inicialmente, o módulo de controle do dispositivo médico 57 envia um sinal de início para o módulo de controle de frequência 55 e obtém medições de corrente e potência do módulo de cálculo 53. O módulo de controle do dispositivo médico 57 então verifica os valores obtidos para assegurar que a carga 39 não seja um circuito aberto ou um curto-circuito. Se não for, então o módulo de controle do dispositivo médico 57 começa a variar o ponto de ajuste de potência para executar a cauterização desejada. A figura 8 é um gráfico que ilustra a maneira na qual o módulo de controle do dispositivo médico 57 pode variar a potência de ponto de ajuste para executar o procedimento de cauterização desejada. Várias outras técnicas e algoritmos de fornecimento de potência podem também ser usados.
[00041] Conforme mostrado na figura 8, durante um período inicial 71 o módulo de controle do dispositivo médico 57 pulsa a potência de ponto de ajuste entre zero e cerca de 10 Watts. Em seguida, durante um período principal de cauterização 73 (que tipicamente dura cerca de 5 segundos) o módulo de controle do dispositivo médico 57 pulsa a potência de ponto de ajuste entre zero e 50 Watts. Durante esse período, o dispositivo de controle médico recebe as medições de potência e de tensão do módulo de cálculo 53 e calcula a partir desses valores a impedância da carga 39. O módulo de controle do dispositivo médico 57 determina que a cauterização está concluída quando a impedância calculada excede um limite. Finalmente, o módulo de controle do dispositivo médico 57 executa um procedimento de término durante um período de encerramento 75. Durante o procedimento de término, o módulo de controle do dispositivo médico 57 varia a potência de ponto de ajuste e certifica-se de que a cauterização foi realizada (verificando a impedância da carga com o uso dos valores medidos de potência e de corrente) e entra novamente no período principal de cauterização se determinar que a cauterização não foi concluída. Design do circuito ressonante
[00042] Será descrita a seguir a maneira como os valores dos indutores e capacitores foram escolhidos nessa modalidade. Conforme será compreendido pelos versados na técnica, podem ser utilizadas outras metodologias de design.
[00043] A impedância complexa do circuito mostrado na figura 2 pode ser aproximada usando-se a seguinte equação: Onde: Rcarga_ref é a resistência de carga referida como o primário (pelo quadrado da razão entre espiras); Rs representa a resistência em série equivalente do indutor, do capacitor do transformador e dos dispositivos de chaveamento.
[00044] As não idealidades de todos os outros componentes são ignoradas e o transformador é considerado ideal como uma primeira aproximação.
[00045] Presumindo que Rs seja um valor pequeno, quando a carga é um circuito aberto (isto é, Rcarga_ref é infinito) a frequência de ressonância pode ser mostrada como sendo:
[00046] De modo similar, quando a carga é um curto-circuito (isto é, Rcarga_ref é zero) a frequência de ressonância pode ser mostrada como sendo:
[00047] Presumindo que Rs seja um valor pequeno: em cada frequência entre fmin e fmax há um valor da carga, Rcarga no qual a maior potência pode ser dissipada na carga. Essa potência máxima pode ser mostrada como um valor grande em frequências próximas de fmin e fmax, e tem um valor mínimo na frequência crítica, fc. Essa potência é chamada de Pmax_fc. Começando com (1) pode-se mostrar que a seguinte relação é válida: onde Vs é a tensão de alimentação.
[00050] A partir de (6 pode-se mostrar que fmin<fc<fmax. Se o circuito for operado na frequência fc, então a equação (4) fornece um limite superior na potência fornecida de pior cenário entre uma faixa de cargas.
[00051] A partir de (1), pode-se mostrar que a eficiência do circuito em ressonância pode ser escrita como:
[00053] isto é, quando (5) tem efeito. Portanto, o sistema é projetado para operar em torno do ponto de máxima eficiência.
[00054] Para esta modalidade específica do design, foram escolhidos os seguintes parâmetros: • Foi utilizada uma tensão de bateria de 24 V, embora a tensão da bateria diminua com a descarga e a carga, de modo que Vs_sq=18 V (pico de onda quadrada em relação à tensão de crista) • Pcarga = 45 W (potência máxima para a carga) • Vcarga = 85 Vrms (tensão máxima para a carga) • Icarga = 1, 4 Arms (corrente máxima para a carga) • fc = 430 kHz (frequência de chaveamento central ou crítica) • fmax = 500 kHz (frequência de chaveamento máxima, que é a frequência de ressonância superior) • fmin β 380 kHz (frequência de chaveamento mínima aproximada - precisa ser calculada)
[00056] Os circuitos ressonantes produzem formas de onda senoidais e, portanto, a tensão de onda quadrada de entrada (Vs_sq) precisa ser convertida no RMS da frequência de chaveamento fundamental (Vs).
[00057] A potência para a carga (Pcarga) é definida por Lm. Com o uso de (4), a indutância de magnetização do transformador (Lm) pode ser determinada. Isso assegura que na frequência crítica, fc, a potência necessária será fornecida:
[00060] Para manter o ajuste, o circuito é operado acima da ressonância de modo que os valores reais de Cs serão tipicamente 20% mais altos para trazer o ponto de operação de volta para baixo (se fosse escolhida uma operação abaixo da ressonância, Cs teria de ser reduzido).
[00061] Conforme anteriormente mencionado, a eficiência é maximizada quando Rcarga_ref é igual à reatância de magnetização na frequência crítica (equação 5). E desejável, portanto, operar em torno da região intermediária da faixa de potência constante (mostrada na figura 5b). Rcarga_sup é a resistência de carga na qual a potência constante varia com a tensão constante. De modo similar, Rcarga_inf é a resistência de carga na qual a potência constante varia com a corrente constante.
[00062] Toma-se a média geométrica dessas resistências de carga para determinar Rcarga_c (resistência de carga central ou crítica)
[00063] Conforme discutido, para uma eficiência máxima, Rcarga_ref deve corresponder à impedância da reatância de magnetização de referência do primário na frequência fc. Portanto, Rcarga deve ser igual à reatância de magnetização de referência do secundário. Lsec pode, então, ser calculado da seguinte forma:
[00065] Para qualquer design industrial particular, pode ser necessário ajustar os valores devido às seguintes razões: • otimizar a eficiência • compensar o efeito não-ideal dos componentes (por exemplo, resistência em série, capacitância & indutância parasítica, características não-ideais do transformador, como indutância de dispersão) • tornar o design prático (por exemplo, usar valores padrão de capacitores e um número inteiro de espiras • permitir margens para os requisitos devido a tolerâncias dos componentes, temperatura, etc.
[00066] Nessa modalidade específica, os valores dos componentes foram otimizados para: Cs = 82 nF Lm = 1,1 uH Ls = 1,4 uH N = 5 que resulta em Lsec ~ 24 uH
[00067] As subseções a seguir descrevem brevemente como esses valores dos componentes foram implementados fisicamente.
[00068] É desejável um capacitor de baixa perda para minimizar as perdas e assegurar que o componente não seja superaquecido. Os capacitores cerâmicos são ideais e o tipo dielétrico de COG/NPO foi utilizado nessa modalidade. A classificação de tensão do capacitor também é importante, uma vez que não deve ser excedida sob todas as condições de carga. Dez capacitores cerâmicos COG/NPO 1206 de 250 V 8,2 nF conectados em paralelo foram usados nessa modalidade. Indutor e transformador
[00069] Nessa modalidade, Ferroxcube 3F3 E32/6/20, uma combinação de núcleo eletrônico/placa, foi usado como um núcleo de ferrita. Ferroxcube 3F3 é fornecido pela Ferroxcube, uma subsidiária de Yageo Corporation, Taiwan. É um material de ferrita de alta frequência otimizado para frequências entre 200 kHz e 500 kHz. o uso desse material permite minimizar as perdas de núcleo. As perdas de núcleo aumentam fortemente com o aumento da densidade de fluxo. Em um indutor, para o armazenamento de uma determinada energia necessária, a densidade de fluxo aumenta com a diminuição da folga de ar (a folga de ar é a separação entre o núcleo eletrônico & placa). Portanto, a folga de ar e o número de espiras podem ser aumentados para reduzir as perdas de núcleo, mas isso deve ser balanceado com o valor real da indutância exigida e a maior quantidade de perdas resistivas introduzidas com o comprimento maior do fio/trilho.
[00070] As mesmas questões aplicam-se ao transformador, exceto que as perdas de núcleo devem-se à tensão de saída e ao número de espiras. Como a tensão de saída é fixa, o número de espiras é a única variável que pode ser alterada mas, novamente, isso deve ser balanceado com as perdas resistivas. Depois que o número de espiras é ajustado, a folga de ar pode, então, ser ajustada para o Lm definido. Qualquer que seja o núcleo utilizado, é uma prática melhor preencher o espaço dos enrolamentos com a maior quantidade possível de cobre para minimizar as perdas resistivas. No transformador, o volume dos enrolamentos é, de preferência, aproximadamente igual no primário e no secundário para equilibrar as perdas.
[00071] As perdas resistivas podem, em geral, ser facilmente calculadas, mas como o circuito está operando a cerca de 400 kHz, profundidade da pele torna-se um problema. A profundidade da pele no cobre a 400 kHz é de apenas cerca de 0,1 mm, de modo que um condutor sólido mais espesso que esse valor não resulta no uso de todo o cobre. Um fio Litz (fio de cobre trançado, isolado e enrolado, em que cada cordão é mais delgado que a profundidade da pele) pode ser usado para reduzir esse efeito. Nessa modalidade, foram usados trilhos de circuito impresso de 2 onças (trilhos de cobre de cerca de 0,07 mm de espessura) para os enrolamentos do indutor (Ls) e do transformador para evitar a necessidade de enrolar componentes personalizados. O indutor tinha duas espiras com uma folga de ar de 0,5 mm entre o núcleo eletrônico e a placa. O transformador tinha uma espira no primário e cinco espiras no secundário com uma folga de ar entre o núcleo eletrônico e a placa de 0,1 mm.
[00072] Um dispositivo médico de cauterização foi descrito anteriormente. Conforme será compreendido pelos versados na técnica, várias modificações podem ser feitas e algumas dessas serão descritas a seguir. Outras modificações ficarão evidentes aos versados na técnica.
[00073] Na modalidade acima, foram descritas várias frequências, correntes e tensões de operação. Conforme será compreendido pelos versados na técnica, os valores exatos de correntes, tensões, frequências, valores de capacitores, valores de indutores, etc., podem ser todos variados dependendo da aplicação, e os valores descritos acima não devem ser considerados como limitadores. Entretanto, em termos gerais, o circuito descrito acima foi projetado para fornecer um sinal de acionamento de RF para um dispositivo médico, em que a potência fornecida é uma potência desejada de ao menos 10 W e, de preferência, entre 10 W e 200 W; a tensão fornecida é uma potência desejada de ao menos 20 Vrms e, de preferência, entre 30 Vrms e 120 Vrms; a corrente fornecida é projetada para ser ao menos 0,5 Arms e, de preferência, entre 1 Arms e 2 Arms; e a frequência de acionamento é de ao menos 50 kHz.
[00074] Na modalidade acima, o circuito ressonante 28 foi formado a partir de elementos de capacitor-indutor-indutor. Conforme será compreendido pelos versados na técnica, o circuito ressonante 28 pode ser formado a partir de vários designs de circuito. A figura 9 ilustra um outro design de circuito ressonante que pode ser usado em outras modalidades. No design mostrado na figura 9, o circuito ressonante 28 é formado a partir de elementos de capacitor-indutor- capacitor, com a carga sendo conectada no segundo capacitor 78. Conforme mostrado, nesse design, não há transformador e, portanto, não há avanço de tensão. Todavia, a operação dessa modalidade ainda seria a mesma que na modalidade descrita anteriormente e, portanto, uma descrição adicional será omitida. Outros designs de circuito ressonante com múltiplos capacitores e indutores em várias configurações em série e em paralelo ou circuitos ressonantes LC mais simples podem também ser usados.
[00075] A figura 1 ilustra uma maneira na qual as baterias e os componentes eletrônicos de controle podem ser montados no interior do cabo do dispositivo médico. Conforme será compreendido pelos versados na técnica, o fator de forma do cabo pode ter muitos designs diferentes.
[00076] Na modalidade acima, foi descrito um algoritmo de controle exemplificador para executar a cauterização do vaso ou tecido seguro pelo fórceps. Conforme será compreendido pelos versados na técnica, podem ser usados vários procedimentos diferentes e recomenda-se ao leitor que consulte a literatura que descreve a operação de dispositivos de cauterização para obter mais informações.
[00077] Na modalidade acima, o sinal de acionamento de RF gerado pelo circuito de acionamento foi aplicado diretamente às duas garras do fórceps do dispositivo médico. Em uma modalidade alternativa, o sinal de acionamento pode ser aplicado a uma garra, sendo que o retorno ou plano terra é fornecido através de uma conexão separada no tecido ou vaso a ser cauterizado.
[00078] Nas modalidades acima, as garras do fórceps foram usadas como os eletrodos do dispositivo médico. Em um dispositivo alternativo, os eletrodos podem ser fornecidos separadamente das garras.
[00079] Nas modalidades acima, duas chaves de FET foram usadas para converter a tensão de CC fornecida pelas baterias em um sinal alternado na frequência de RF desejada. Conforme será compreendido pelos versados na técnica, não é necessário usar duas chaves - pode ser usada uma chave, ou múltiplas chaves podem ser usadas conectadas, por exemplo, em uma configuração de ponte. Adicionalmente, embora tenham sido usadas chaves de FET, podem ser usados outros dispositivos de chaveamento, como chaves bipolares. Entretanto, os MOSFETs (transistores de efeito de campo metal-óxido semicondutor) são preferenciais devido ao seu desempenho superior em termos de baixas perdas quando operam nos níveis de frequência e de corrente descritos anteriormente.
[00080] Na modalidade acima, o circuito ressonante 28 agiu como um atenuador dependente da frequência. O circuito ressonante foi projetado como um atenuador substancialmente sem perdas, mas isso não é essencial. O circuito ressonante pode incluir, também, componentes com perdas, embora o circuito resultante será, certamente, menos eficiente.
[00081] Na modalidade acima, o circuito de amostragem 51 I & Q obteve amostras do sinal de tensão/corrente detectado uma vez a cada período e combinou as amostras de períodos adjacentes. Conforme será compreendido pelos versados na técnica, isso não é essencial. Devido à natureza sincronizada da amostragem, as amostras podem ser tomadas mais de uma vez por período ou uma vez a cada n° período se for desejado. A taxa de amostragem usada na modalidade acima foi escolhida para otimizar a taxa na qual as medições foram disponibilizadas para o módulo de controle do dispositivo médico 57, uma vez que isso permite um controle melhor da potência aplicada durante o processo de cauterização.
[00082] Na modalidade acima, foi fornecida uma fonte CC de 24 V. Em outras modalidades, podem ser fornecidas fontes de tensão de CC mais baixas. Nesse caso, pode ser fornecida uma razão entre espiras maior do transformador para aumentar a tensão de carga a um nível desejado, ou podem ser usadas tensões de operação mais baixas.
[00083] Na modalidade acima, foi utilizada uma técnica de amostragem sincronizada para se obter medições da tensão de carga e da corrente de carga. Conforme será compreendido pelos versados na técnica, isso não é essencial e podem ser usadas outras técnicas de amostragem mais convencionais.
[00084] Na modalidade acima, o dispositivo médico foi configurado par fornecer uma potência desejada aos eletrodos do efetor de extremidade. Em uma modalidade alternativa, o dispositivo pode ser configurado para fornecer um nível desejado de corrente ou de tensão aos eletrodos do efetor de extremidade.
[00085] Na modalidade acima, a bateria é mostrada integral com o dispositivo médico. Em uma modalidade alternativa, a bateria pode ser um conjunto de baterias, de modo a ser presa no cinto do cirurgião ou simplesmente ser colocada no suporte Mayo. Nessa modalidade, um cabo relativamente pequeno de dois condutores faria a conexão do conjunto de baterias com o dispositivo médico.
Claims (10)
1. Dispositivo médico (1) caracterizado pelo fato de que compreende: um cabo (5) para preensão por um usuário; um efetor de extremidade (7) acoplado ao cabo (5) e tendo ao menos um contato elétrico; um circuito gerador de radiofrequência (RF) (17, 20) acoplado ao cabo (5) e operável para gerar um sinal de acionamento de RF e para fornecer o sinal de acionamento de RF ao pelo menos um contato elétrico, em que o circuito gerador de RF (17, 20) compreende um circuito ressonante; e um circuito de controle configurado para variar a frequência do sinal de acionamento de RF, em que o circuito de controle é operável para receber uma medição do sinal de acionamento de RF e é operável para variar a frequência do sinal de acionamento de RF para controlar pelo menos uma dentre potência, tensão, e corrente fornecida ao pelo menos um contato elétrico do efetor de extremidade (7), em que a medição é obtida de um circuito de amostragem que faz amostragem de um sinal de tensão ou corrente detectado em uma frequência de amostragem que varia em sincronismo com a frequência e fase do sinal de acionamento de RF.
2. Dispositivo, de acordo com a reivindicação 1, caracterizado pelo fato de que o circuito gerador de radiofrequência (17, 20) compreende um circuito de chaveamento que gera um sinal ciclicamente variável, tal como um sinal de onda quadrada, de uma fonte CC e em que o circuito ressonante é configurado para receber o sinal ciclicamente variável.
3. Dispositivo, de acordo com a reivindicação 1 ou 2, caracterizado pelo fato de que compreende um compartimento para bateria para contenção de uma ou mais baterias para fornecer energia ao circuito gerador de RF (17, 20) para gerar o sinal de acionamento de RF.
4. Dispositivo, de acordo com a reivindicação 3, caracterizado pelo fato de que o compartimento para bateria é configurado para conter um módulo compreendendo as uma ou mais baterias e o circuito gerador de RF (17, 20).
5. Dispositivo, de acordo com a reivindicação 1, caracterizado pelo fato de que o circuito gerador de RF (17, 20) compreende: um circuito de chaveamento para gerar um sinal ciclicamente variável a partir de uma diferença de potencial dentre os terminais da bateria; e um circuito de acionamento ressonante acoplado ao circuito de chaveamento e operável para filtrar o sinal ciclicamente variável gerado pelo circuito de chaveamento; e em que o sinal de acionamento de RF é controlado por uma saída do circuito de acionamento ressonante.
6. Dispositivo, de acordo com a reivindicação 1, caracterizado pelo fato de que a frequência na qual o circuito de amostragem é operável para obter amostra do sinal detectado é uma fração de número inteiro da frequência do sinal de acionamento de RF.
7. Dispositivo, de acordo com qualquer das reivindicações 1 a 6, caracterizado pelo fato de que o circuito de controle é configurado para variar a frequência do sinal de acionamento de RF em torno de uma frequência de ressonância do circuito ressonante.
8. Dispositivo, de acordo com a reivindicação 7, caracterizado pelo fato de que a característica de ressonância do circuito ressonante varia com uma carga conectada ao pelo menos um contato elétrico e em que o circuito de controle é configurado para variar a frequência de acionamento de RF para rastrear alterações na característica de ressonância do circuito ressonante.
9. Dispositivo, de acordo com a reivindicação 1, caracterizado pelo fato de que o circuito gerador de RF (17, 20) compreende um gerador de sinal operável para gerar um sinal ciclicamente variável na frequência de RF; e um atenuador dependente de frequência que atenua o sinal ciclicamente variável em dependência mediante a frequência do sinal ciclicamente variável.
10. Dispositivo, de acordo com a reivindicação 9, caracterizado pelo fato de que o atenuador dependente de frequência compreende um circuito ressonante tendo uma frequência de ressonância na, ou próxima da, frequência de RF do sinal ciclicamente variável.
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CA2806164C (en) | 2018-09-25 |
CN103025259A (zh) | 2013-04-03 |
BR112012033478A8 (pt) | 2022-02-08 |
EP2571438B1 (en) | 2018-10-24 |
RU2012155688A (ru) | 2014-06-27 |
BR112012033478A2 (pt) | 2016-11-29 |
CN103025259B (zh) | 2016-06-29 |
EP2571438A1 (en) | 2013-03-27 |
US20130345689A1 (en) | 2013-12-26 |
SG186808A1 (en) | 2013-02-28 |
WO2011144911A1 (en) | 2011-11-24 |
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