BR112016014030B1 - Aparelho eletrônico para uso em um dispositivo médico e dispositivo médico - Google Patents
Aparelho eletrônico para uso em um dispositivo médico e dispositivo médico Download PDFInfo
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Abstract
parelho eletrônico e dispositivo médico. a presente invenção refere-se a um dispositivo médico (1) que é descrito tendo um cabo (5), uma haste (3) acoplada ao cabo e um atuador de extremidade (7) acoplado à haste. em uma modalidade, o dispositivo inclui um transdutor ultrassônico (8) e é disposto de modo que a energia ultrassônica ou elétrica possa ser liberada para um vaso ou tecido a ser tratado. vários circuitos de detecção (31, 33) inovadores são descritos para permitir uma medição do sinal de acionamento a ser feita e retroalimentada novamente para um controlador (23). um circuito de fusível ativo (130) também é descrito para proteger uma ou mais baterias (15) do dispositivo de uma situação de sobrecorrente.
Description
[001] A presente invenção se refere 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.
[002] Muitos procedimentos cirúrgicos requerem cortar ou ligar vasos sanguíneos ou outro tecido interno e muitos procedimentos são realizados usando-se técnicas minimamente invasivas com um dispositivo de cauterização portátil para realizar o corte ou ligação. Alguns dispositivos de cauterização portáteis existentes usam um transdutor ultrassônico no dispositivo de cauterização para aplicar energia ultrassônica ao tecido a ser cortado ou ligado. Outros dispositivos de cauterização portáteis aplicam energia RF diretamente ao tecido/vaso sendo cauterizado através do fórceps do dispositivo.
[003] A presente invenção tem como objetivo fornecer um dispositivo cirúrgico alternativo que é capaz de aplicar energia ultrassônica ou energia RF ao vaso ou tecido a ser cauterizado. Outros aspectos da invenção se referem à forma na qual o circuito de controle é fornecido para selecionar entre os diferentes modos operacionais. Outros aspectos da invenção se referem à forma na qual as medidas de tensão e corrente podem ser feitas no design do circuito para emitir relatório a um controlador, como um microprocessador, e à forma na qual o circuito de controle pode ser fornecido para garantir que corrente em excesso não seja drenada da bateria.
[004] De acordo com um aspecto, a presente invenção fornece um dispositivo médico que compreende: um atuador de extremidade para prender um vaso/tecido; um transdutor ultrassônico acoplado ao atuador de extremidade; um circuito de acionamento acoplado ao atuador de extremidade e ao transdutor ultrassônico e operável para gerar um sinal de acionamento periódico e para fornecer o sinal de acionamento para o transdutor ultrassônico ou para o atuador de extremidade e um controlador operável para controlar o circuito de acionamento de modo que o sinal de acionamento seja aplicado a um que for desejado dentre o transdutor ultrassônico e o atuador de extremidade.
[005] Em uma modalidade, o circuito de acionamento compreende um primeiro circuito ressonante tendo uma primeira frequência de ressonância e um segundo circuito ressonante tendo uma segunda frequência de ressonância que é diferente da primeira frequência de ressonância, sendo que a primeira frequência de ressonância corresponde a uma característica ressonante do transdutor ultrassônico e sendo que o controlador é operável para controlar o circuito de acionamento de modo que o circuito de acionamento gere um sinal de acionamento tendo uma frequência que corresponde à primeira frequência de ressonância, quando o sinal de acionamento deve ser aplicado ao transdutor ultrassônico, e de modo que o circuito de acionamento gere um sinal de acionamento tendo uma frequência correspondendo à segunda frequência de ressonância, quando o sinal de acionamento deve ser aplicado ao atuador de extremidade.
[006] Um gerador de sinal pode também ser fornecido de modo que seja acoplado entre o controlador e o circuito de acionamento para gerar uma tensão cíclica de uma fonte de tensão CC dependendo dos sinais de controle do controlador e para fornecer a tensão cíclica ao primeiro e ao segundo circuitos ressonantes do circuito de acionamento.
[007] O controlador pode ser disposto para variar o período do sinal de acionamento ao redor da primeira frequência de ressonância ou da segunda frequência de ressonância para variar a energia fornecida ao vaso ou tecido preso pelo atuador de extremidade. O controlador pode variar o período do sinal de acionamento de modo que a frequência do sinal de acionamento varie ao redor da primeira frequência de ressonância dentro de 0,1% a 1% da primeira frequência de ressonância; ou de modo que a frequência do sinal de acionamento varie ao redor da segunda frequência de ressonância dentro de 40% a 60% da segunda frequência de ressonância.
[008] Tipicamente, as características de ressonância do primeiro e do segundo circuitos ressonantes variam com o tecido ou vaso preso pelo fórceps e, em uma modalidade, o controlador é configurado para variar o período do sinal de acionamento para rastrear as alterações na respectiva característica de ressonância.
[009] Um guia de ondas ultrassônicas pode ser fornecido que é acoplado ao transdutor ultrassônico para guiar a energia ultrassônica gerada pelo transdutor ultrassônico em direção ao atuador de extremidade. O atuador de extremidade pode compreender a primeira e a segunda garras, e o segundo circuito ressonante pode ser acoplado eletricamente à primeira e à segunda garras do atuador de extremidade. Por exemplo, a primeira garra do atuador de extremidade pode ser acoplada eletricamente ao guia de ondas, e o segundo circuito ressonante pode ser acoplado eletricamente à primeira garra do atuador de extremidade através do guia de ondas ultrassônicas. Em algumas modalidades, o primeiro circuito ressonante é acoplado eletricamente ao transdutor ultrassônico e ao guia de ondas.
[0010] O circuito de detecção pode ser fornecido para detectar um sinal de acionamento aplicado ao transdutor ultrassônico ou ao atuador de extremidade. Em uma modalidade, um ou ambos dentre o primeiro e o segundo circuitos ressonantes podem compreender ao menos um dentre uma bobina indutora, um capacitor e um resistor, e sendo que o circuito de detecção pode compreender um circuito amplificador operacional (AmpOp) para detectar a tensão ao longo da bobina indutora ou do capacitor ou do resistor e para converter a tensão detectada em um sinal do sensor adequado para inserção no controlador. Em uma modalidade alternativa, um ou ambos dentre o primeiro e o segundo circuitos ressonantes podem compreender um elemento de impedância que é conectado entre o circuito ressonante e um potencial de referência, e sendo que o circuito de detecção compreende um circuito divisor para obter uma medição da tensão ao longo do elemento de impedância e um gerador de sinal de polarização para aplicar um sinal de polarização CC à medição da tensão. Nesse caso, o elemento de impedância pode compreender um capacitor ou um resistor. Tipicamente, o circuito de detecção compreende o circuito de bloqueamento de CC para evitar o acoplamento do sinal de polarização de CC do gerador de sinal de polarização ao circuito de acionamento. O gerador do sinal de polarização pode compreender um circuito divisor de tensão conectado entre uma tensão de referência e uma tensão da fonte do controlador.
[0011] O dispositivo é, de preferência, um dispositivo operado à bateria e compreende uma ou mais baterias para alimentar o dispositivo e compreende adicionalmente um circuito de fusível ativo para proteger a uma ou mais baterias. O circuito de fusível ativo pode compreender uma chave acoplada eletricamente entre um terminal da uma ou mais baterias, e o circuito de acionamento e o circuito de controle configurados para abrir a chave para isolar o terminal de alimentação do circuito de acionamento.
[0012] A presente invenção também fornece um dispositivo médico que compreende: um atuador de extremidade para prender um vaso/tecido; um circuito de acionamento para gerar um sinal de acionamento cíclico para conduzir energia para o vaso/tecido; circuito de detecção para detectar um sinal de acionamento gerado pelo circuito de acionamento e um controlador responsivo ao circuito de detecção e operável para controlar o circuito de acionamento para controlar a energia liberada para o vaso/tecido; sendo que o circuito de acionamento compreende um elemento de impedância que é acoplado a um potencial de referência e sendo que o circuito de detecção compreende um circuito divisor para obter uma medição da tensão ao longo do elemento de impedância e um gerador de sinal de polarização para aplicar um sinal de polarização de CC à medição da tensão.
[0013] O elemento de impedância pode ser um capacitor ou um resistor. O circuito de detecção pode compreender também o circuito de bloqueio de CC para evitar o acoplamento do sinal de polarização de CC do gerador de sinal de polarização ao circuito de acionamento. O gerador do sinal de polarização pode compreender um circuito divisor conectado entre uma tensão de referência e uma tensão da fonte do controlador. O circuito divisor do gerador de sinal de polarização pode ser conectado à tensão da fonte do controlador através de uma chave e sendo que o controlador é configurado para abrir a chave quando o controlador não precisar de sinais do circuito de detecção.
[0014] A presente invenção também fornece um dispositivo médico que compreende: um atuador de extremidade para prender um vaso/tecido; uma ou mais baterias para fornecer uma alimentação de tensão CC; um gerador de sinal acoplado à uma ou mais baterias para gerar um sinal de acionamento cíclico a partir da fonte de tensão CC para guiar a energia para o vaso/tecido; um controlador operável para controlar o gerador de sinal para controlar a energia liberada para o vaso/tecido e um circuito de fusível ativo acoplado entre a uma ou mais baterias e o gerador de sinal para proteger a uma ou mais baterias.
[0015] O circuito de fusível ativo pode compreender uma chave, que está acoplada eletricamente entre um terminal da uma ou mais baterias e o gerador de sinal, e o circuito de controle configurado para comutar a chave. A chave pode ser disposta para desconectar o gerador de sinal da uma ou mais baterias ou pode conectar uma impedância grande entre o gerador de sinal e a uma ou mais baterias.
[0016] O circuito de controle do fusível ativo pode compreender o circuito para detectar uma medição da corrente sendo drenada da uma ou mais baterias e é configurado para chavear a chave, caso essa medição de corrente exceda um limite. O circuito de controle do fusível ativo pode compreender um comparador para comparar a medição da corrente com o limite e sendo que uma saída do comparador controla a abertura e o fechamento da chave.
[0017] A presente invenção também fornece um método para operação de um dispositivo médico, que compreende gerar um sinal de acionamento periódico e aplicar o sinal de acionamento a um transdutor ultrassônico ou a um atuador de extremidade do dispositivo médico e controlar o circuito de acionamento de modo que o sinal de acionamento seja aplicado a um que for desejado dentre o transdutor ultrassônico e o atuador de extremidade.
[0018] A presente invenção também fornece um método para cauterizar ou cortar um vaso ou tecido, método que compreende: prender o vaso ou tecido com um atuador de extremidade de um dispositivo médico; usar um circuito de acionamento para aplicar um sinal de acionamento periódico a um transdutor ultrassônico ou ao atuador de extremidade e controlar o circuito de acionamento de modo que o sinal de acionamento seja aplicado a um que for desejado dentre o transdutor ultrassônico e o atuador de extremidade. O método pode usar o dispositivo médico da descrição acima.
[0019] A presente invenção também fornece um aparelho eletrônico para uso em um dispositivo médico tendo um transdutor ultrassônico e um atuador de extremidade, aparelho eletrônico que compreende: um circuito de acionamento para gerar um sinal de acionamento periódico; e um controlador operável para controlar o circuito de acionamento de modo que o sinal de acionamento seja aplicado a um que for desejado dentre o transdutor ultrassônico e o atuador de extremidade; sendo que o circuito de acionamento compreende um primeiro circuito ressonante tendo uma primeira frequência de ressonância e um segundo circuito ressonante tendo uma segunda frequência de ressonância, que é diferente da primeira frequência de ressonância, e sendo que o controlador é operável para controlar o circuito de acionamento de modo que o circuito de acionamento gere um sinal de acionamento tendo uma frequência que corresponde à primeira frequência de ressonância quando o sinal de acionamento deve ser aplicado ao transdutor ultrassônico, e de modo que o circuito de acionamento gere um sinal de acionamento tendo uma frequência correspondendo à segunda frequência de ressonância quando o sinal de acionamento deve ser aplicado ao atuador de extremidade.
[0020] A presente invenção também fornece um dispositivo médico que compreende: um atuador de extremidade para prender um vaso/tecido; um circuito de acionamento acoplado ao atuador de extremidade e operável para gerar um sinal de acionamento para fornecer o sinal de acionamento para o atuador de extremidade; um controlador operável para gerar e emitir sinais de controle ao circuito de acionamento para controlar o sinal de acionamento gerado pelo circuito de acionamento; sendo que o circuito de acionamento e uma carga formada pelo vaso/tecido preso pelo atuador de extremidade definem um circuito ressonante cuja frequência de ressonância varia à medida que a impedância da carga formada pelo vaso/tecido preso pelo atuador de extremidade muda; sendo que o controlador é disposto para gerar sinais de controle que fazem com que o circuito de acionamento gere um sinal de acionamento tendo uma frequência que rastreia a dita frequência de ressonância à medida que muda e sendo que o dito controlador é adicionalmente disposto para reduzir um ou mais dentre a potência, corrente ou tensão liberadas para a carga formada pelo vaso/tecido preso pelo atuador de extremidade.
[0021] O circuito sensor pode ser fornecido para detectar sinais aplicados à carga formada pelo vaso/tecido preso pelo atuador de extremidade e para medir o circuito para processar os sinais do circuito sensor para determinar uma medição da impedância da carga formada pelo vaso/tecido preso pelo atuador de extremidade. Nesse caso, o controlador pode gerar os ditos sinais de controle dependendo da dita medição da impedância da carga formada pelo vaso/tecido preso pelo atuador de extremidade.
[0022] Em uma modalidade, o controlador gera sinais de controle tendo sequências de pulsos, e o controlador omite um ou mais pulsos dos sinais de controle para reduzir uma ou mais dentre a potência, corrente ou tensão liberadas para a carga formada pelo vaso/tecido preso pelo atuador de extremidade.
[0023] Tipicamente, nesse caso, o controlador compreende um gerador de sinal de pulso que gera pulsos a uma frequência desejada que depende da dita frequência de ressonância, e o controlador omite os pulsos gerados pelo dito gerador de sinal de pulso através da supressão dos pulsos gerados pelo gerador de sinal de pulso.
[0024] 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:
[0025] a Figura 1 ilustra um dispositivo de cauterização portátil que tem baterias e circuito de acionamento e controle montados em uma porção de cabo do dispositivo;
[0026] a Figura 2 é um diagrama de blocos parcial ilustrando os principais componentes do dispositivo de cauterização usado em uma modalidade da invenção;
[0027] a Figura 3 é um diagrama do circuito ilustrando os principais componentes elétricos do dispositivo de cauterização mostrados na Figura 2;
[0028] a Figura 4 é uma ilustração esquemática da forma na qual o transdutor ultrassônico é acoplado ao guia de ondas para liberar a energia ultrassônica gerada para o fórceps e ilustrar a forma na qual o circuito mostrado na Figura 3 pode liberar energia elétrica ao fórceps;
[0029] a Figura 5 é um diagrama de blocos de uma ilustração esquemática dos módulos de processamento que formam parte do microprocessador mostrado na Figura 2;
[0030] a Figura 6 ilustra a forma dos sinais de controle gerados pelo microprocessador para controlar o circuito de acionamento enquanto minimiza o 3o conteúdo harmônico;
[0031] a Figura 7 é um gráfico de contorno ilustrando a potência liberada em função da resistência da carga e da frequência de acionamento;
[0032] a Figura 8a é um diagrama de circuito ilustrando um modo no qual uma medição da corrente da carga pode ser determinada e fornecida ao microprocessador;
[0033] a Figura 8b é um diagrama de circuito ilustrando um modo no qual uma medição da corrente da carga pode ser determinada e fornecida ao microprocessador;
[0034] a Figura 8c é um diagrama de circuito ilustrando um modo no qual uma medição da corrente da carga pode ser determinada e fornecida ao microprocessador;
[0035] a Figura 9a é um diagrama de circuito ilustrando um modo no qual uma medição da corrente da carga pode ser determinada e fornecida ao microprocessador sem usar um circuito AmpOp;
[0036] a Figura 9b é um diagrama de circuito ilustrando um modo no qual uma medição da corrente da carga pode ser determinada e fornecida ao microprocessador e ilustrando um modo no qual uma medição da corrente da carga pode ser determinada e fornecida ao microprocessador sem usar um circuito AmpOp e
[0037] a Figura 10 é um diagrama de circuito ilustrando um circuito de fusível ativo usado para proteger as baterias mostradas na Figura 2 da demanda excessiva de corrente.
[0038] 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 fórceps ultrassônico-cirúrgico ou fórceps eletrocirúrgico, um cirurgião pode cauterizar, coagular/dessecar e/ou simplesmente reduzir o sangramento controlando a energia ultrassônica aplicada ao tecido/vaso por um transdutor ultrassônico ou controlando a energia RF aplicada ao tecido/vaso através do fórceps.
[0039] A Figura 1 ilustra a forma de um dispositivo médico ultrassônico/cirúrgico RF 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 de peça única que tem uma haste alongada 3 com um cabo 5 conectado à extremidade proximal da haste 3 e um atuador de extremidade 7 conectado à extremidade distal da haste 3. Nessa modalidade, o atuador de extremidade 7 compreende o fórceps médico 9 que é controlado pelo usuário manipulando as alavancas de controle 11 e 13 do cabo 5.
[0040] Durante um procedimento cirúrgico, a haste 3 é inserida através de um trocarte para obter acesso ao interior do paciente e ao local de operação. O cirurgião vai manipular o fórceps 9 usando o cabo 5 e as alavancas de controle 11 e 13 até que o fórceps 9 esteja localizado ao redor do vaso a ser cortado ou cauterizado. A energia elétrica é, então, aplicada, de forma controlada, ou diretamente ao tecido através do fórceps 9 (como energia RF) ou a um transdutor ultrassônico 8 que é montado dentro do cabo 5 e acoplado ao fórceps 9 através de um guia de ondas (não mostrado) dentro da haste 3, para realizar o corte/cauterização usando a energia ultrassônica. Conforme mostrado na Figura 1, nessa modalidade, o cabo 5 também aloja as baterias 15 e os componentes eletrônicos de controle 17 para gerar e controlar a energia elétrica necessária para fazer a cauterização. Dessa maneira, o dispositivo 1 é uma peça única 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. Entretanto, esse quadro de controle separado pode ser fornecido, se desejado.
[0041] A Figura 2 é um diagrama de bloco esquemático ilustrando o circuito elétrico principal do dispositivo de cauterização/corte 1 usado nessa modalidade para gerar e controlar a energia elétrica fornecida ao transdutor ultrassônico ou ao fórceps 9. Conforme será explicado em mais detalhes abaixo, nesta modalidade, o circuito é projetado para controlar o período de uma forma de onda do acionador elétrico que é gerada para controlar a quantidade de potência liberada para o tecido/vaso sendo cauterizado.
[0042] Conforme mostrado na Figura 2, o dispositivo de cauterização/corte 1 compreende uma interface de usuário 21, através da qual o usuário recebe informações (como uma indicação de que a energia está sendo aplicada ao tecido/vaso preso pela energia elétrica ou energia ultrassônica) e através da qual o usuário controla a operação do dispositivo de cauterização/corte 1, incluindo a seleção da operação ultrassônica ou operação RF. Conforme mostrado, a interface de usuário 21 é acoplada a um microprocessador 23 que controla o procedimento de corte/cauterização gerando sinais de controle que são emitidos para o circuito de acionamento de porta 25. Em resposta aos sinais de controle do microprocessador 23, o circuito de acionamento de porta 25 gera sinais de controle de porta que fazem com que um gerador de sinal de ponte 27 gere uma forma de onda de acionamento desejada que é aplicada ou ao transdutor ultrassônico 8 ou ao fórceps 9 através de um circuito de acionamento. O circuito de detecção de tensão 31 e o circuito de detecção de corrente 33 geram medições da corrente e da tensão aplicadas ao transdutor ultrassônico 8 ou ao fórceps 9, que eles alimentam de volta ao microprocessador 23 para propósitos de controle. A Figura 2 também mostra as baterias 15 que fornecem a potência para alimentar o circuito elétrico mostrado na Figura 2. Nessa modalidade, as baterias 15 estão dispostas para alimentar os trilhos de 0 V e 14 V.
[0043] A Figura 3 ilustra em mais detalhes os componentes do circuito de acionamento de porta 25, o gerador de sinal de ponte 27 e o circuito de acionamento 29. A Figura 3 mostra também um circuito elétrico equivalente 30 do transdutor ultrassônico piezelétrico 8 e a carga (Rcarga) formada pelo tecido/vaso a ser tratado. Conforme mostrado na Figura 3, o circuito de acionamento de porta 25 inclui dois acionadores de porta FET37, acionador de porta FET 37-1 e acionador de porta FET 37-2. Um primeiro conjunto de sinais de controle (CTRL1) do microprocessador 23 é fornecido ao acionador de porta FET 37-1 e um segundo conjunto de sinais de controle (CTRL2) do microprocessador 23 é fornecido ao acionador de porta FET 37-2. O acionador de porta FET 37-1 usa o primeiro conjunto de sinais de controle (CTRL1) para gerar dois sinais de acionamento, um para acionar cada dos dois FETs 41-1 e 41-2 do gerador de sinal de ponte 27. O acionador de porta FET 37-1 gera sinais de acionamento que fazem com que o FET superior (41-1) seja ligado quando o FET inferior (41-2) está desligado ou vice-versa. Isso faz com que o nó A seja conectado alternativamente ao trilho de 14 V (quando FET 41-1 está ligado) e ao trilho de 0 V (quando FET 41-2 está ligado). De modo similar, o acionador de porta FET 37-2 usa o segundo conjunto de sinais de controle (CTRL2) para gerar dois sinais de acionamento - um para acionar cada um dos dois FETs 41-3 e 41-4 do gerador de sinal de ponte 27. O acionador de porta FET 37-2 gera sinais de acionamento que fazem com que o FET superior (41-3) seja ligado quando o FET inferior (41-4) está desligado ou vice-versa. Isso faz com que o nó B seja conectado alternativamente ao trilho de 14 V (quando FET 41-3 está ligado) e ao trilho de 0 V (quando o FET 41-4 está ligado). Dessa forma, os dois conjuntos de sinais de controle (CTRL1 e CTRL2) emitidos pelo microprocessador 23 controlam a forma de onda digital que é gerada e aplicada entre os nós A e B. Cada conjunto de sinais de controle (CTRL1 e CTRL2) compreende um par de linhas de sinal, uma para indicar quando o FET do lado superior está ligado e outra para indicar quando o FET do lado inferior está ligado. Dessa forma, o microprocessador 23, ou através de software ou através de uma função de hardware dedicado, pode assegurar que a condição indesejável quando ambos os FETs do lado superior e inferior estão simultaneamente ligados não ocorra. Na prática, isso exige deixar um tempo ocioso quando ambos os FET do lado superior e inferior estão desligados para assegurar que, mesmo quando atrasos de chaveamento variáveis são permitidos, não há possibilidade de que ambos os FETs possam estar ligados simultaneamente. Na presente modalidade, o tempo ocioso de cerca de 100 ns foi usado.
[0044] Conforme mostrado na Figura 3, os nós A e B estão conectados ao circuito de acionamento 29, assim, a tensão digital gerada pelo gerador de sinal de ponte 27 é aplicada ao circuito de acionamento 29. A tensão aplicada fará com que a corrente flua no circuito de acionamento 29. Conforme mostrado na Figura 3, o circuito de acionamento 29 inclui dois circuitos transformadores 42-1 e 42-2. O primeiro circuito transformador 42-1 é projetado para acionamento eficiente do transdutor ultrassônico 8 e inclui um circuito ressonante capacitor-indutor-indutor 43-1 formado pelo capacitor CUSs 45, indutor LUSs 47 e indutor LUSm 49. Ao acionar o transdutor ultrassônico 8, o microprocessador 23 é disposto para gerar sinais de controle para o circuito de acionamento de porta 25 de modo que a frequência fundamental (fd) da tensão digital aplicada pelos nós A e B seja próxima da frequência de ressonância do circuito ressonante 43-1, que é, nesta modalidade, de cerca de 50 kHz. Como resultado da característica ressonante do circuito ressonante 43-1, a tensão digital aplicada ao longo dos nós A e B fará com que uma corrente substancialmente senoidal na frequência fundamental (fd) flua dentro do circuito ressonante 43-1. Isso se deve ao fato de que o conteúdo harmônico maior da tensão do acionador será atenuado pelo circuito ressonante 43-1 e pela impedância de Lt e Ct1 encaminhada ao primário do transformador.
[0045] Conforme ilustrado na Figura 3, o indutor LUSm 49 forma o primário do circuito transformador 42-1, cujo secundário é formado pelo indutor LUSsec 53. O transformador converte a tensão do acionador (VUSd) ao longo do indutor Lm 49 em uma tensão de carga (VL; tipicamente de cerca de 120 volts) que é aplicada ao transdutor ultrassônico 8. As características elétricas do transdutor ultrassônico 8 mudam com a impedância das garras do fórceps e qualquer tecido ou vaso preso pelo fórceps 9; e a Figura 3 mostra o transdutor ultrassônico 8 e a impedância das garras do fórceps e qualquer tecido ou vaso preso pelo fórceps 9 pelo indutor Lt 57, os capacitores paralelos Ct1 59 e Ct2 61 e a resistência Rcarga.
[0046] O indutor LUSs e o capacitor CUSs do circuito de acionamento 29 são projetados para ter um produto LC correspondente ao do indutor Lt e do capacitor Ct1 do transdutor ultrassônico 8. Correlacionar o produto LC de uma série de redes LC assegura que a frequência da ressonância da rede seja mantida. De modo similar, a reatância magnética do indutor LUSm é escolhida de modo que, na ressonância, ela corresponda à reatância capacitiva do capacitor Ct2 do transdutor ultrassônico 8. Por exemplo, se o transdutor 8 é definido de modo que o Ct2 tem uma capacitância de cerca de 3,3 nF, então, o indutor LUSm deve ter uma indutância de cerca de 3 mH (a uma frequência de ressonância de cerca de 50 kHz). A projeção do circuito de acionamento 29, dessa forma, fornece eficiência de acionamento ótima em termos de fornecimento de energia ao tecido/vaso preso pelo fórceps 9. O aprimoramento na eficiência é obtido por causa da corrente fluindo em CUSs e, consequentemente, a ponte FET (27) é reduzida, porque a corrente magnetizando o transformador anula a corrente fluindo em Ct2. Além disso, por causa dessa anulação da corrente, a corrente fluindo em CUSs é proporcional à corrente fluindo em Rcarga, que permite que a corrente de carga seja determinada através da medição da corrente fluindo em CUSs.
[0047] O segundo circuito transformador 42-2 é projetado para acionamento eficiente da energia elétrica RF diretamente para o tecido/vaso através do fórceps 9 e inclui um circuito ressonante capacitor-indutor-indutor 43-2 formado pelo capacitor CFs 46, indutor LFs 48 e indutor LFm 50. Ao acionar o fórceps 9 diretamente com energia elétrica, o microprocessador 23 é disposto para gerar sinais de controle para o circuito de acionamento de porta 25 de modo que a frequência fundamental (fd) da tensão digital aplicada ao longo dos nós A e B seja próxima da frequência de ressonância do circuito ressonante 43-2, que é, nesta modalidade, de cerca de 500 kHz. Como resultado da característica ressonante do circuito ressonante 43-2, a tensão digital aplicada ao longo dos nós A e B fará com que uma corrente substancialmente senoidal na frequência fundamental (fd) flua dentro do circuito ressonante 43-2. Isso se deve ao fato de que o conteúdo harmônico maior da tensão do acionador será atenuado pelo circuito ressonante 43-2.
[0048] Conforme ilustrado na Figura 3, o indutor LFm 50 forma o primário do circuito transformador 42-1, cujo secundário é formado pelo indutor LUSsec 54. O transformador converte a tensão do acionador (VFd) ao longo do indutor LFm 50 em uma tensão de carga (VFL; tipicamente de cerca de 120 volts) que é aplicada ao fórceps 9. O tecido ou vaso preso pelas garras do fórceps 9 é representado como uma carga de resistência Rcarga na caixa marcada 9 na Figura 3. Na prática, esta será a mesma carga resistiva que é ilustrada no circuito elétrico equivalente 30 do transdutor ultrassônico 8.
[0049] A Figura 4 é um diagrama esquemático ilustrando a forma na qual o transdutor ultrassônico 8 se acopla ao tecido/vaso a ser cauterizado e a forma na qual os componentes do circuito ilustrado na Figura 3 se conectam ao transdutor ultrassônico 8 e ao fórceps 9. Em particular, a Figura 4 mostra a haste 3, o fórceps 9 e o transdutor ultrassônico 8. A Figura 4 também mostra o guia de ondas 72 ao longo do qual o sinal ultrassônico que é gerado pelo transdutor ultrassônico 8 é guiado. O guia de ondas 72 é conectado ao nó "BB", mostrado na Figura 3, enquanto a alimentação de entrada do transdutor ultrassônico 8 está conectada ao nó "AA" mostrado na Figura 3. O nó de saída "CC" do segundo circuito transformador 42-2 é conectado a uma parede interna condutora da bainha 3 que é eletricamente conectada à garra superior 74 do fórceps 9. O caminho de retorno é através do tecido/vaso a ser cauterizado e a garra inferior 76, que é eletricamente conectada ao nó "BB".
[0050] Quando o sinal de acionamento tem uma frequência de acionamento de cerca de 50 kHz, muito pouca corrente fluirá dentro do segundo circuito transformador 42-2 porque a frequência de acionamento está longe da frequência de ressonância do circuito ressonante 43-2, de modo que a impedância de entrada do segundo circuito transformador 42-2 será muito alta para esse sinal de acionamento. Portanto, a potência será liberada quase que inteiramente através do primeiro circuito transformador 42-1. Da mesma forma, quando o sinal de acionamento tiver uma frequência de acionamento de cerca de 500 kHz, muito pouca corrente fluirá dentro do primeiro circuito transformador 42-1 porque a frequência de acionamento está longe da frequência de ressonância do circuito ressonante 43-1, de modo que a impedância de entrada do primeiro circuito transformador 42-1 será muito alta para esse sinal de acionamento. Portanto, a potência será liberada quase que inteiramente através do segundo circuito transformador 42-2. Dessa forma, os dois circuitos transformadores 421 e 42-2 podem ser acionados por um gerador de sinal de ponte comum 27; embora também seja possível acionar cada circuito transformador com geradores de sinal de ponte separados.
[0051] Nem sempre é desejável aplicar potência total ao tecido/vaso a ser tratado. Dessa forma, nesta modalidade no modo ultrassônico de operação, a quantidade de energia ultrassônica fornecida ao vaso/tecido é controlada mediante a variação do período da forma de onda digital aplicada ao longo dos nós A e B, de modo que a frequência de acionamento (fd) se mova na direção contrária da frequência de ressonância do transdutor ultrassônico 8. Isso funciona porque o transdutor ultrassônico 8 age como um atenuador dependente (sem perdas) de frequência. Quanto mais próximo o sinal de acionamento está da frequência de ressonância do transdutor ultrassônico 8, mais energia ultrassônica o transdutor ultrassônico 8 vai gerar. De modo similar, à medida que a frequência do sinal de acionamento se move na direção contrária à frequência de ressonância do transdutor ultrassônico 8, menos energia ultrassônica é gerada pelo transdutor ultrassônico 8. Além de ou em vez de, a duração dos pulsos dos sinais de acionamento pode ser variada para controlar a quantidade de energia ultrassônica liberada para o tecido/vaso.
[0052] De modo similar, no modo elétrico de operação, a quantidade de potência elétrica fornecida ao fórceps 9 é controlada mediante a variação do período da forma de onda digital aplicada ao longo dos nós A e B, de modo que a frequência de acionamento (fd) se move na direção contrária da frequência de ressonância do circuito ressonante 43-2. Isso funciona porque o circuito ressonante 43-1 age como um atenuador dependente (sem perdas) de frequência. Quanto mais próximo o sinal de acionamento está da frequência de ressonância do transdutor ultrassônico 43-1, menos o sinal de acionamento é atenuado. Por outro lado, à medida que a frequência do sinal de acionamento se move na direção contrária à frequência de ressonância do circuito 43-1, mais o sinal de acionamento é atenuado e, assim, a energia elétrica fornecida ao tecido/vaso reduz. A frequência de acionamento precisa se afastar da frequência de ressonância em cerca de 50% da frequência de ressonância para obter a faixa desejada de variação de potência. Uma abordagem alternativa para controlar a potência, a corrente ou tensão aplicada durante o modo elétrico da operação é ajustar continuamente a frequência do sinal de excitação para mantê-lo correlacionado à frequência de ressonância do circuito de acionamento (já que ele muda com a variação na impedância da carga) e, portanto, mantém a operação eficiente, e omitir alguns dos pulsos dos sinais de controle de acionamento até que a potência, corrente e/ou tensão fiquem abaixo do limite relevante.
[0053] Uma outra alternativa, que é mais eficaz quando se usa a técnica de omissão de pulso, é remover o indutor 48 mostrado na Figura 3 e, portanto, o circuito de acionamento do modo elétrico de operação se torna um circuito ressonante LC substancialmente paralelo (não é um circuito ressonante LC paralelo puro porque a indutância de vazamento do transformador aparece em série com o indutor 48 e não pode ser inteiramente removida). A vantagem de se remover o indutor 48 é que a eficiência total pode ser aumentada porque não há mais perdas no indutor. Uma outra vantagem é que o tamanho físico do circuito pode ser reduzido porque o indutor frequentemente é um componente fisicamente grande em relação aos FETs, ao microprocessador, aos capacitores e a outros componentes do sistema.
[0054] O microprocessador 23 controla a liberação de potência com base na potência desejada a ser liberada ao circuito 30 (que modela o transdutor ultrassônico 8 e o tecido/vaso preso pelo fórceps 9) ou ao fórceps 9 e com base nas medições da tensão de carga (VL) e da corrente de carga (iL) obtidas a partir do circuito de detecção de tensão 31 e o circuito de detecção de corrente 33. O microprocessador 23 também seleciona a frequência do sinal de acionamento (ao redor de 50 kHz ou ao redor de 500 kHz) com base em uma entrada do usuário recebida através da interface de usuário 21 que seleciona ou a operação elétrica ou a operação ultrassônica.
[0055] A Figura 5 é um diagrama de blocos ilustrando os principais componentes do microprocessador 23 que é usado nesta modalidade. Conforme mostrado, o microprocessador 23 inclui o circuito de amostragem síncrono I, Q 81 que recebe a tensão detectada e os sinais de corrente do circuito de detecção 31 e 33 e obtém as amostras correspondentes que são passadas para um módulo de processamento de tensão e corrente medidas 83. O módulo de processamento de tensão e de corrente medidas 83 usa as amostras recebidas para calcular a impedância de, a tensão RMS aplicada a e a corrente RMS fluindo por, o transdutor ultrassônico 8 e/ou diretamente ao tecido/vaso preso pelo fórceps 9 e, a partir dos mesmos, a potência que está atualmente sendo fornecida ao circuito 30 ou diretamente ao tecido/vaso preso pelo fórceps 9. Os valores determinados são então passados para um controlador de potência 85 para processamento adicional. O módulo de processamento de tensão e de corrente medidas 83 pode também processar as amostras I e Q recebidas para calcular a diferença de fase entre a tensão da carga (VL) e a corrente da carga (iL). Durante o modo ultrassônico de operação, na ressonância, essa diferença de fase deve ser ao redor de zero e assim essa medição de fase pode ser usada como um parâmetro de retroinformação para o controlador de potência 85.
[0056] O controlador de potência 85 usa o valor de impedância recebida e o valor da potência liberada para determinar, de acordo com um algoritmo predefinido e um valor do ponto de ajuste de potência e um sinal de indicação de modo (recebido de um módulo de controle do dispositivo médico 89 e indicando a operação ultrassônica ou operação elétrica), um período/frequência desejados (Δtnovo) dos sinais de controle (CTRL1 e CTRL2) que são usados para controlar o circuito de acionamento de porta 25. O período/frequência desejado é passado do controlador de potência 85 para o gerador de sinal de controle 95, que altera os sinais de controle CTRL1 e CTRL2 para alterar o período da forma da onda para corresponder ao período desejado. Os sinais de controle CTRL podem compreender sinais de onda quadrada tendo o período desejado ou podem compreender pulsos periódicos com o período correspondendo ao período desejado (Δtnovo) e com o tempo relativo dos pulsos dos sinais de controle sendo definido para minimizar o conteúdo harmônico da forma de onda que é gerada pelo gerador de sinal de ponte 27 (de modo a minimizar a 3a harmônica de ordem). Nesta modalidade, os sinais de controle CTRL1 são emitidos para o acionamento da porta FET 37-1 (mostrada na Figura 2), que amplia os sinais de controle e então os aplica aos FETs 41-1 e 41-2; e os sinais de controle CTRL2 são emitidos para o acionamento da porta FET 37-2 (mostrada na Figura 2), que amplia os sinais de controle e então aplica aos FETs 41-3 e 41-4, para, assim, gerar a forma de onda desejada com o novo período (Δtnovo).
[0057] Para acionar o circuito com a forma de onda RMS ótima, os MOSFETs 41 são acionados como pares opostos e complementares. Embora a tensão de saída máxima seja atingida quando os pares MOSFETs são acionados em uma mudança de fase de 180 graus, o conteúdo harmônico resultante dessa forma de onda de acionamento, particularmente, a 3a harmônica (que é excluída de forma eficaz pelo filtro de saída), é bastante alto. Os inventores descobriram que a mudança de fase ótima entre os sinais de controle aplicados aos dois pares de MOSFETs 41, para a 3a redução harmônica, é cerca de 120°. Isso é ilustrado na Figura 6 que mostra no gráfico superior a saída do primeiro par de MOSFET 41-1 e 41-2; no gráfico do meio, a saída do segundo par de MOSFET 41-3 e 41-4 (deslocado em 120° em relação ao gráfico superior); e, no gráfico inferior, a tensão de saída resultante (normalizada) aplicada pelas entradas A e B. O formato dessa tensão de saída normalizada tem um conteúdo harmônico de 3a ordem muito baixo. Amostragem de sinal I & Q
[0058] Tanto a tensão da carga quanto a corrente da carga serão formas de onda substancialmente senoidal, embora elas possam estar fora de fase, dependendo da impedância da carga representada pelo transdutor 8 e/ou o vaso/tecido preso pelo fórceps 9. A corrente da carga e a tensão da carga terão a mesma frequência de acionamento (fd) correspondendo ao período de forma de onda presentemente definido (Δtnovo). Normalmente, na amostragem de um sinal, o circuito de amostragem opera de modo assíncrono em relação à frequência do sinal cuja amostra está sendo obtida. Entretanto, o microprocessador 23 sabe que a frequência e fase dos sinais de chaveamento, o circuito de amostragem síncrono 81 pode obter amostras do sinal de tensão/corrente medido em pontos predefinidos no tempo durante o período de acionamento. Nesta modalidade, durante o modo ultrassônico da operação, o circuito de amostragem síncrono 81 faz uma superamostragem do sinal medido, oito vezes por período, para obter quatro amostras de I e quatro amostras de Q. A superamostragem permite a redução de erros causados pela distorção harmônica e, portanto, permite a determinação mais precisa dos valores de corrente e tensão medidas. Entretanto, a superamostragem não é essencial e, assim, uma subamostragem (menos de duas amostras por período) é realizada quando o dispositivo está operando no modo elétrico de operação e é possível devido à natureza síncrona da operação de amostragem. O tempo no qual o circuito de amostragem síncrono 81 toma essas amostras é controlado, nesta modalidade, pelos sinais de controle CTRL1 e CTRL2. Dessa forma, quando o período de tempo desses sinais de controle é alterado, o período de tempo dos sinais de controle da amostragem CTRL1 e CTRL2 também muda (enquanto suas fases relativas permanecem iguais). Dessa forma, o circuito de amostragem 81 muda continuamente o tempo de amostragem dos sinais de tensão e corrente detectados, à medida que o período de tempo da forma de onda de acionamento é alterado de modo que as amostras sejam sempre tomadas nos mesmos pontos de tempo dentro do período de tempo da forma de onda de acionamento. Portanto, o circuito de amostragem 81 realiza uma operação de amostragem "síncrona" 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. É claro que essa operação de amostragem convencional também poderia ser usada.
[0059] As amostras obtidas pelo circuito de amostragem síncrona 51 são passadas para o módulo de processamento de tensão e corrente medidas 83 que pode determinar a magnitude e a fase do sinal medido de apenas uma amostra "I" e uma amostra "Q" da corrente de carga e da tensão de carga. Entretanto, nesta modalidade, para se obter uma média, o módulo de processamento 83 obtém a média consecutiva de amostras "I" para fornecer um valor "I" médio e amostras "Q" consecutivas para fornecer um valor "Q" médio e, então, usa os valores I e Q médios para determinar a magnitude e a fase do sinal medido. É claro que deve ser reconhecido que algum pré-processamento dos dados pode ser necessário para converter as amostras I e Q medidas reais da tensão da carga ou corrente da carga, por exemplo, a relação, integração ou diferenciação dos valores da amostra pode ser realizada para converter os valores de amostra em amostras verdadeiras da tensão da carga (VL) e da corrente da carga (iL). Onde é necessária a integração ou diferenciação, isso pode ser obtido simplesmente trocando a ordem das amostras I e Q, já que a integração/diferenciação de um sinal senoidal envolve simplesmente uma alteração e uma mudança de 90 graus na fase.
[0060] A tensão da carga RMS, a corrente da carga e a potência liberada, ppode, podem ser determinadas a partir de:
[0061] A impedância da carga representada pelo transdutor ultrassônico 8 e pelo vaso/tecido presos pelo fórceps 9 (ou apenas a impedância do fórceps 9 e do vaso/tecido presos pelo fórceps 9, se a energia elétrica for diretamente aplicada ao fórceps 9) pode ser determinada a partir de:
[0062] Uma forma alternativa de calcular ^cargae xcarga é da seguinte forma: e a diferença de fase entre a tensão da carga e a corrente da carga podem ser determinadas a partir de:
[0063] Uma aproximação matematicamente eficaz da função atan2 pode ser feita usando-se tabelas de consulta e interpolação na aritmética de ponto fixo ou usando-se um algoritmo similar a "CORDIC". Limites
[0064] Como em qualquer sistema, há certos limites que podem ser colocados na potência, corrente e tensão que podem ser liberados ou para o transdutor ultrassônico 8 ou para o fórceps 9. Os limites usados nessa modalidade e a maneira como são controlados serão descritos a seguir.
[0065] Nesta modalidade, o circuito de acionamento 29 é projetado para liberar energia ultrassônica ao tecido e para liberar energia elétrica ao tecido com os seguintes requisitos:
[0066] 1) Alimentada com uma alimentação 14 V CC nominal
[0067] 2) Forma de onda de saída substancialmente senoidal em aproximadamente 50 kHz no caso de operação ultrassônica
[0068] 3) Forma de onda de saída substancialmente senoidal em aproximadamente 500 kHz no caso de operação elétrica RF
[0069] 4) Saída limitada de potência de 90 W no caso de operação ultrassônica
[0070] 5) Saída limitada de potência de 100 W no caso de operação elétrica
[0071] 6) Corrente limitada a 1,4 Arms e tensão limitada a 130 Vrms no caso de operação ultrassônica
[0072] 7) Corrente limitada a 1,4 Arms e tensão limitada a 100 Vrms no caso de operação elétrica
[0073] 8) No caso de operação ultrassônica, a fase medida é maior que um limite de fase definido por sistema
[0074] O controlador de potência 85 mantém os dados definindo esses limites e os usa para controlar a decisão de aumentar ou reduzir o período da forma de onda ou de omitir pulsos dos sinais de controle dadas as últimas potência medida, impedância da carga e/ou fase medida. Nesta modalidade, quando se opera no modo ultrassônico de operação, o limite de fase que é usado depende da impedância da carga medida. Em particular, o controlador de potência 85 mantém uma tabela de consulta (não mostrada) relacionando a impedância da carga ao limite de fase e os valores nessa tabela limitam a fase de modo que quando a impedância da carga medida é baixa (indicando que as garras do fórceps 9 estão abertas e não estão prendendo o tecido ou um vaso), a potência liberada é reduzida (de preferência para zero).
[0075] Conforme descrito acima, uma das formas de controlar a operação do dispositivo (quando operando no modo elétrico de operação) é maximizar a eficiência do acionamento. Quando controla o dispositivo dessa forma, o controlador de potência 85 rastreia uma condição de liberação de potência máxima, à medida que a carga muda. A forma na qual isso pode ser feito será descrita agora. Condição de rastreamento de liberação de potência máxima
[0076] A impedância complexa do circuito mostrado na Figura 3 (quando operando no modo elétrico de operação e com o indutor 48 removido) pode ser aproximada pela seguinte equação: Onde:
[0077] Rcarga_ref é a resistência da carga encaminhada para o primário (pelo quadrado da razão de voltas); e Rs representa a resistência de série equivalente do indutor, do capacitor, do transformador e dos dispositivos de chaveamento. A impedância complexa pode ser reescrita como:
[0080] Quando a frequência de acionamento (f) corresponde à frequência de ressonância dessa impedância complexa, a parte imaginária 'SPZ) - 0. Portanto, o controlador de potência 85 pode variar a frequência de acionamento (f) para manter a parte imaginária em ou ao redor de zero usando um laço de bloqueio de fase. De fato, pode ser mostrado quando 3(Z) = o a potência máxima (para uma dada tensão de alimentação) é liberada à carga.
[0081] A Figura 7 é um gráfico de contorno mostrando os contornos da potência que pode ser liberada para a carga em função da frequência de acionamento e da resistência de carga (Rcarga). Conforme mostrado na Figura 7, a potência que pode ser liberada varia com a resistência da carga e a frequência de acionamento. A Figura 7 também mostra a linha 92 da liberação da potência máxima que pode ser obtida à medida que a resistência de carga e a frequência de acionamento mudam. Portanto, o controlador de potência 85 pode usar o valor medido da Rcarga juntamente com os dados armazenados definindo a linha 92 mostrada na Figura 7 (que pode ser uma tabela de consulta) para determinar a frequência de acionamento correspondente a ser usada. Dessa forma, o microprocessador 23 vai rastrear ao longo da linha 92 mostrada na Figura 7, à medida que a resistência da carga muda durante o processo de corte/cauterização.
[0082] Uma das vantagens dessa abordagem é que permite uma condição de operação útil em valores baixos de Rcarga, em particular, para valores de Rcarga menores que o valor crítico (isto é, quando Rcar9a_ref <2^Z,FM), no qual uma potência máxima será liberada mesmo que seja abaixo do nível de potência desejado. Entretanto, a operação ao longo da linha 92 da liberação de potência máxima pode resultar no rompimento de alguns dos limites do sistema acima a menos que uma ação de controle adicional seja tomada. Na modalidade preferencial, essa ação de controle adicional é para usar técnicas de omissão de pulso até que a potência, corrente e/ou tensão médias estejam abaixo do limite relevante. Por exemplo, como pode ser observado a partir das medições descritas acima, a tensão medida e o módulo de processamento de corrente 83 podem determinar a potência liberada, a tensão RMS e a corrente RMS. O controlador de potência 85 pode, portanto, usar esses valores para omitir um ou mais pulsos dos sinais de controle CTRL até que os valores da tensão e corrente medidos estejam abaixo dos limites do sistema relevantes e a potência liberada esteja em ou abaixo do ponto de ajuste de potência definido pelo módulo de controle de dispositivos médicos 89.
[0083] Os pulsos podem ser omitidos, por exemplo, passando os pulsos gerados pelo gerador do sinal de controle 87 através de uma porta lógica (não mostrada) e suprimindo seletivamente pulsos que são gerados pelo gerador de sinal de controle 87 controlando o nível de lógica de uma outra entrada para a porta lógica. Por exemplo, os pulsos de cada sinal de controle que é gerado pelo gerador de sinal de controle 87 podem ser passados por uma porta AND com uma outra entrada da porta AND sendo gerada pelo controlador de potência 85 e sendo uma lógica "1" quando os pulsos devem ser emitidos para os acionamentos de porta FET como normal e sendo uma lógica "0" quando os pulsos são omitidos ou suprimidos. Outras técnicas de omissão de pulso podem ser também usadas. Módulo de controle do dispositivo médico
[0084] Conforme mencionado acima, o módulo de controle do dispositivo médico 89 controla a operação geral do dispositivo de cauterização/corte 1. Ele recebe dados do usuário através do módulo de entrada de dados pelo usuário 91. Esses dados inseridos podem especificar que as garras do fórceps 9 estão agora prendendo um vaso ou tecido e que o usuário quer começar a cortar/cauterizar e especificar se a energia ultrassônica ou a energia elétrica deve ser aplicada ao vaso/tecido. Em resposta, nesta modalidade, o módulo de controle do dispositivo médico 89 inicia um procedimento de controle de corte/cauterização. Inicialmente, o módulo de controle do dispositivo médico 89 envia um sinal de iniciação ao controlador de potência 85 e obtém as medições de impedância da carga determinadas pelo módulo de processamento de tensão e corrente 83. O módulo de controle do dispositivo médico 89, então, verifica a impedância da carga obtida para garantir que a carga não esteja em circuito aberto ou curto-circuito. Se não estiver, então, o módulo de controle do dispositivo médico 89 começa a variar o ponto de ajuste de potência para fazer o corte/cauterização desejados e define o período/frequência do sinal de acionamento inicial a ser gerado. Conforme discutido acima, para a operação ultrassônica, a frequência inicial do sinal de acionamento será definida ao redor de 50 kHz e para operação elétrica de RF, a frequência inicial será definida ao redor de 500 kHz. Circuito de detecção de tensão/corrente
[0085] Conforme mostrado na Figura 2, o circuito de detecção de tensão 31 é fornecido para detectar a tensão da carga aplicada à carga, e o circuito de detecção de corrente 33 é fornecido para detectar a corrente aplicada à carga. Os sinais detectados são fornecidos ao microprocessador 23 para uso no controle da operação do dispositivo médico. Há várias formas de detectar a tensão da carga e a corrente da carga, e algumas delas serão agora descritas.
[0086] A Figura 8a ilustra o lado primário do primeiro circuito transformador 42-1 e uma forma pela qual o circuito de detecção de corrente 33 obtém uma medição da corrente da carga. Conforme mostrado, o circuito de detecção de corrente 33 compreende uma volta no indutor adicional 67 que liga o fluxo presente no indutor 47 (ou indutor 49) e que consequentemente emite uma tensão ao longo do indutor 67 que varia com a taxa de alteração da corrente da carga. A tensão ao longo do indutor 67 é uma tensão bipolar cuja amplitude é diretamente proporcional à taxa de alteração da corrente de carga e ao número de voltas em 67. Essa tensão bipolar é ajustada e convertida em tensão unipolar adequada para ser inserida no microprocessador 23 pelo circuito AmpOp 69-1 que emite uma tensão medida (Vmedida). Essa tensão medida também dependerá da corrente que flui para o indutor 47 e assim também dependerá da corrente fluindo do lado secundário do circuito transformador 42-1 e, dessa forma, a corrente fluindo através da carga. À medida que o número de voltas do indutor 47 para o indutor 67 é conhecida, o módulo de processamento da tensão e da corrente medidas 83 pode usar a Vmedida para determinar a tensão ao longo do indutor 47. A tensão ao longo do indutor 47 está relacionada à corrente fluindo através do indutor 47 por V=Ldi/dt. Como a indutância do indutor 47 é conhecida, o módulo de processamento de tensão e de corrente medidas 83 pode determinar a corrente fluindo no lado primário do circuito do transformador 42-1 integrando a tensão ao longo do indutor 47 e ajustando o resultado para corresponder à indutância do indutor 47 (e o ajuste do circuito AmpOp 69-1). Essa medição de corrente pode então ser convertida em uma medição adequada da corrente de carga (iL) com um ajuste adicional para levar em consideração o número de voltas entre o indutor 49 e o indutor 53. É claro que o módulo de processamento de tensão e de corrente medidas 83 não precisa integrar a tensão ao longo do indutor 47, já que os sinais medidos são senoidais e, assim, a integração pode ser obtida aplicando-se um fator de ajuste e uma mudança de fase de 90 graus adequados. Dessa forma, módulo de processamento de tensão e de corrente medidas 83 pode determinar a corrente da carga aplicando um fator de ajuste (pré-armazenado) à tensão medida (Vmedida) e aplicando uma mudança de fase de 90 graus adequada (que pode ser obtida simplesmente trocando a ordem das amostras I e Q, conforme discutido acima).
[0087] A Figura 8b ilustra o lado primário do primeiro circuito transformador 42-1 e outra forma pela qual o circuito de detecção de corrente 33 pode obter uma medição da corrente da carga. Conforme mostrado, nesse caso, o circuito de detecção de corrente 33 mede a tensão ao longo do capacitor 45. A tensão ao longo do capacitor 45 é uma tensão bipolar. Essa tensão bipolar é ajustada e convertida em tensão unipolar adequada para ser inserida no microprocessador 23 pelo circuito AmpOp 69-2 que emite uma tensão medida (Vmedida). Essa tensão é relacionada à corrente fluindo do lado primário do circuito do transformador 42 por I=CdVmedida/dt e, dessa forma, à corrente fluindo através da carga. Como a capacitância do capacitor 45 é conhecida, o módulo de processamento de tensão e de corrente medidas 83 pode determinar a corrente fluindo no lado primário do circuito do transformador 42-1 diferenciando a tensão ao longo do capacitor 45 e ajustando o resultado para corresponder à capacitância do capacitor 45 (e o ajuste do circuito AmpOp 69-2). Essa medição de corrente pode então ser convertida em uma medição adequada da corrente de carga (iL) com um ajuste adicional para levar em consideração o número de voltas entre o indutor 49 e o indutor 53. É claro que o módulo de processamento de tensão e de corrente medidas 83 não precisa diferenciar a tensão ao longo do capacitor 45, já que os sinais medidos são senoidais e, assim, a diferenciação pode ser obtida aplicando-se um fator de ajuste e uma mudança de fase de 90 graus adequados. Dessa forma, módulo de processamento de tensão e de corrente medidas 83 pode determinar a corrente da carga aplicando um fator de ajuste (pré-armazenado) à tensão medida (Vmedida) e aplicando uma mudança de fase de 90 graus adequada (que pode ser obtida simplesmente trocando a ordem das amostras I e Q, conforme discutido acima).
[0088] A Figura 8c ilustra esquematicamente como uma medida da tensão da carga pode ser determinada. A Figura 8c mostra o lado secundário do primeiro circuito transformador 42 e ilustra o uso de um circuito divisor de tensão (nesse caso formado pelos resistores R1 e R2) com a tensão ao longo do resistor R2 sendo liberada para o circuito AmpOp 69-3. Portanto, aplicando-se uma escala adequada à tensão medida do AmpOp 69-3, o módulo de processamento de tensão e de corrente medidas 83 pode determinar a tensão da carga.
[0089] Os circuitos de detecção descritos acima usam os circuitos AmpOp 69 para converter os sinais de acionamento bipolares em tensões unipolares que são adequadas para inserir no microprocessador 23. O uso desses circuitos AmpOp tem várias desvantagens, incluindo o alto custo, o consumo de potência e a necessidade de espaço dentro dos componentes eletrônicos. Esses são fatores importantes quando o dispositivo é projetado para ser alimentado por bateria e os componentes eletrônicos são alojados no interior do cabo 5 do dispositivo. A Figura 9 ilustra vários circuitos de detecção que podem ser usados sem um AmpOp. O circuito da Figura 9a é adequado quando o sinal de acionamento CA é unipolar. Isso pode ser obtido substituindo-se o gerador de sinal de ponte inteira 27 por um gerador de sinal de meia-ponte. Isso significaria a remoção, por exemplo, dos FETs 41-3 e 41-4 e a conexão do nó B ao aterramento. Nesse caso, o microprocessador 23 precisa apenas de gerar um sinal de controle (CTRL1) para controlar os FETs 41-1 e 41-2. O circuito da Figura 9b é adequado para os sinais de acionamento tanto unipolar quanto bipolar.
[0090] Na Figura 9a, o capacitor 45 foi deslocado para estar entre o indutor 49 que forma o primário do circuito do transformador 42-1 e o aterramento (GND). O circuito de detecção de corrente 33 está disposto para medir a tensão ao longo do capacitor 45 através de um possível divisor formado pelos resistores R1//R2 e R3. O resistor R1 conecta a saída de um capacitor de bloqueio de CC CB a um trilho de tensão de alimentação do microprocessador 23 (nesse caso a 3,3V) através da chave 121; e o resistor R2 conecta a saída do capacitor de bloqueio de CC CB a um potencial de referência (nesse caso, o aterramento). Os resistores R1 e R2, portanto, fornecem um circuito divisor que aplica uma polarização de CC ao sinal CA medido. O capacitor de bloqueio de CC evita que essa polarização de CC se acople ao circuito de acionamento. Tipicamente, os resistores R1 e R2 são iguais de modo que a polarização de CC ficará em 1,65 V. Dessa forma, a tensão de saída do circuito de detecção 33 será uma tensão CA tendo um valor de meio trilho de cerca de 1,65 V e cujo pico de tensão será uma proporção da tensão ao longo do capacitor 45. O divisor de potencial formado pelos resistores R1//R2 e R3 é tal que a amplitude de pico a pico do sinal CA passado para o microprocessador 23 é menor que a faixa de entrada de 3,3 V do microprocessador 23. Se o microprocessador 23 opera em um trilho de tensão diferente (por exemplo, 5 V), então, os valores dos resistores R1, R2 e R3 podem ser ajustados de modo adequado. Para minimizar a corrente drenada tanto do trilho de 3,3 V quanto do circuito do transformador 42-1, os resistores R1, R2 e R3 podem ter valores relativamente altos, e os valores típicos para esses resistores são: R1=R2= 200 Q e R3=1.000 Q. Os valores de R1 e R2 devem ser escolhidos para satisfazer aos requisitos de impedância de entrada do conversor analógico/digital usado para amostragem dos sinais. A chave 121 permite que o microprocessador 23 desconecte o circuito de detecção 33 do trilho de 3,3 V, de modo que quando a detecção não é necessária, o circuito 33 não consume nenhuma potência.
[0091] A Figura 9b ilustra a forma na qual circuitos similares podem ser fornecidos do lado secundário do circuito do transformador 42-1. Em particular, a Figura 9b mostra o circuito de detecção de tensão 31 usado para obter uma medição da tensão da carga VL através de um divisor de tensão formado pelos capacitores C1 e C2. Se os capacitores C1 e C2 fossem substituídos por resistores, então, um capacitor de bloqueio CB deveria ser fornecido antes do circuito divisor formado pelos resistores R1 e R2 da forma mostrada na Figura 9a. A Figura 9b também mostra o circuito de detecção de corrente 33 que detecta a corrente da carga através da detecção da tensão ao longo do capacitor C3 através de um divisor de potencial formado pelos resistores R4//R5 e R6. Conforme mostrado, um capacitor de bloqueio de CC CB é fornecido para permitir que um sinal de polarização de CC seja adicionado à saída do microprocessador através do circuito divisor formado a partir dos resistores R4 e R5. Como antes, as chaves 121-1 e 121-2 permitem que o microprocessador desligue os circuitos de detecção 31 e 33 quando os sinais de sensor não são necessários. Conforme os versados na técnica entenderão, os circuitos de detecção 31 e 33 sem AmpOp ilustrados na Figura 9 são mais econômicos de serem fabricados, podem ser feitos para consumir menos potência e ocupar menos espaço na placa de circuito que os circuitos AmpOp ilustrados na Figura 8.
[0092] Os circuitos ilustrados nas Figuras 8 e 9 foram usados para obter medições do primeiro circuito transformador 42-1 do circuito de acionamento 29. Conforme os versados na técnica entenderão, circuitos de detecção iguais ou similares seriam fornecidos para detectar sinais no segundo circuito transformador 42-2. Adicionalmente, embora os circuitos de detecção ilustrados na Figura 9 detectem a tensão ao longo do capacitor, os circuitos poderiam também detectar a tensão ao longo de outro elemento de impedância, como ao longo de um resistor do circuito transformador 42.
[0093] Tipicamente, com os dispositivos operados à bateria, como o dispositivo médico 1 descrito acima, um fusível é fornecido entre as baterias e o circuito elétrico, para proteger a bateria contra danos causados por curtos-circuitos e similares. Entretanto, os fusíveis convencionais têm uma resistência de cerca de 10 mOhms. Com esse fusível convencional, quando 10A são drenados das baterias, aproximadamente 1 W é dissipado ao longo do fusível. Um circuito de fusível ativo 130 que é usado nessa modalidade será agora descrito com referência à Figura 10, que reduz a dissipação de potência associada a esses fusíveis convencionais.
[0094] A Figura 10 mostra as baterias 15, que alimentam o trilho de 14V e o trilho GND para o circuito mostrado na Figura 3. O circuito de fusível ativo 130 compreende um amplificador diferencial 131 que mede a queda de tensão ao longo de parte de um traço condutor PCB que é conectado entre o trilho de 14 V e o terminal positivo das baterias (Vbat+). O traço condutor 133 tem uma resistência de aproximadamente 1-2 mOhms e, assim, a queda de tensão é proporcional à corrente que está sendo drenada das baterias 15. A queda de tensão medida é filtrada em passa-baixa pelo filtro passa-baixa 136 para evitar picos temporários ativando o circuito do fusível, de modo que apenas a tensão correspondendo à corrente CC drenada das baterias 15 passará através do filtro 135. Nesta modalidade, o filtro passa-baixa 135 tem uma frequência de corte de cerca de 10 Hz. A saída do filtro passa-baixa 135 é então comparada com uma tensão de referência (Vref) usando um comparador com trava 137. A tensão de referência é definida antecipadamente para corresponder a um limite desejado da corrente drenada das baterias. Nesta modalidade, Vref é definida para corresponder a um limite de corrente de 15A. Quando a queda de tensão ao longo do traço 133 é menor que a tensão de referência, a saída do comparador 137 permanece em um valor alto, que mantém a chave do FET 139 ligada e, assim, a corrente pode ser drenada das baterias 15 pelo gerador de sinal de ponte 27. Entretanto, quando a queda de tensão ao longo do traço 133 é maior que a tensão de referência, então, a saída do comparador 137 diminui e é mantida baixa mesmo que a corrente drenada das baterias caia para abaixo do limite definido. Quando a saída do comparador é baixa, o FET 139 é desligado desconectando, assim, as baterias 15 do ao menos o gerador de sinais de ponte 27.
[0095] Nesta modalidade, o FET 139 é uma chave do modo acentuado de N-canais tendo uma resistência de apenas 2 mOhms. Isso significa que quando a chave 139 é ligada e 10A são drenados das baterias, apenas 0,2 W são dissipados ao longo da chave 139.
[0096] Nesta modalidade, quando o comparador 137 é ativado e a chave 139 é desligada (circuito aberto), as baterias 15 têm que ser removidas para reinicializar o circuito de fusível ativo 130, quando a abertura da chave 139 desconecta todos os componentes eletrônicos com exceção dos componentes do circuito do fusível ativo 130 das baterias. Alternativamente, se o microprocessador 23 (ou algum outro circuito de controle) for diretamente alimentado pelas baterias, então, o comparador 137 poderia ser reinicializado em resposta a uma entrada do usuário (por exemplo, em resposta ao usuário pressionar um botão de reinicialização ou similar) ou em resposta a algum outro evento desencadeador (como após um período predeterminado de ausência). Modificações e alternativas
[0097] Um dispositivo médico de cauterização/corte foi descrito acima. 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.
[0098] Na modalidade acima, foram descritas várias frequências, correntes e tensões de operação. Conforme os versados na técnica entenderão, as correntes, tensões, frequências, valores do capacitor, valores do indutor, etc. exatos podem variar dependendo da aplicação e quaisquer valores descritos acima não devem ser considerados limitantes de nenhuma forma. Entretanto, em termos gerais, o circuito descrito acima foi projetado para fornecer um sinal de acionamento a um dispositivo médico, sendo que a potência liberada deve ser de ao menos 10 W e de preferência entre 10 W e 200 W; a tensão liberada deve ser de ao menos 20 VRMS e de preferência entre 30 VRMS e 120 VRMS; a corrente liberada deve ser de ao menos 0,5 ARMS e de preferência entre 1 ARMS e 2 ARMS; e a frequência de acionamento da operação ultrassônica deve ser entre de ao menos 20 kHz e de preferência entre 30 kHz e 80 kHz; e a frequência de acionamento da operação RF deve ser de ao menos 100 kHz e de preferência entre 250 kHz e 1 MHz.
[0099] Na modalidade acima, os circuitos ressonantes 43-1 e 43-2 foram formados a partir dos elementos capacitor-indutor-indutor. Conforme os versados na técnica entenderão, outros designs de circuito ressonante com múltiplos capacitores e indutores em várias configurações em série e paralelas ou circuitos ressonantes LC mais simples podem também ser usados. Além disso, em algumas aplicações não há necessidade de um transformador para intensificar a tensão de acionamento, já que os FETs podem liberar a tensão de acionamento necessária.
[00100] 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 forma do cabo pode ter muitos designs diferentes. De fato, não é essencial para o dispositivo ser alimentado por bateria, embora seja preferencial para algumas aplicações, para evitar a necessidade de cabos de alimentação e similares.
[00101] A modalidade descrita acima inclui uma descrição de várias características novas, incluindo a nova habilidade de aplicar seletivamente energia ultrassônica ou energia RF ao tecido preso pelos fórceps, a nova forma na qual o microprocessador controlou a operação do dispositivo no modo elétrico de operação; a forma na qual a corrente/tensão da carga é medida e a forma na qual as baterias são protegidas usando-se um circuito de fusível ativo. Conforme os versados na técnica entenderão, essas novas características não precisam ser usadas juntas. Por exemplo, as técnicas de detecção de corrente/tensão descritas acima podem ser usadas com outros dispositivos assim como o circuito de fusível ativo. De modo similar, a forma na qual o modo elétrico de operação é controlado rastreando-se a condição de liberação de potência máxima e usando-se técnicas de omissão de pulso pode ser usada em um dispositivo que não tem um transdutor ultrassônico.
[00102] Na modalidade acima, um algoritmo de controle exemplificador para executar o corte/cauterização do vaso ou tecido preso pelos fórceps foi descrito. Conforme os versados na técnica entenderão, vários procedimentos diferentes podem ser usados e o leitor deve consultar a literatura descrevendo a operação de tais dispositivos de corte/cauterização para mais detalhes.
[00103] Na modalidade acima, quatro chaves de FET foram usadas para converter a tensão CC fornecida pelas baterias em um sinal alternado na frequência desejada. Conforme os versados na técnica entenderão, não é necessário usar quatro chaves, duas chaves podem ser usadas (usando-se um circuito de meia-ponte). Adicionalmente, embora as chaves de FET tenham sido usadas, outros dispositivos de chaveamento, como chaves de transistor bipolar, podem ser usados. 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.
[00104] Na modalidade acima, o circuito de amostragem I e Q 81 fez superamostragem do sinal de tensão/corrente detectado no modo ultrassônico de operação e fez subamostragem do sinal de tensão/corrente detectado no modo elétrico de operação. Conforme será compreendido pelos versados na técnica, isso não é essencial. Devido à natureza síncrona da amostragem, as amostras podem ser obtidas mais de uma vez por período ou uma vez a cada nésimo período se necessário. A taxa de amostragem usada na modalidade acima foi escolhida para maximizar a taxa na qual as medições foram disponibilizadas para o controlador de potência 85 e para o módulo de controle do dispositivo médico 89, já que isso permite um controle melhor da potência aplicada durante o processo de cauterização.
[00105] Na modalidade acima, uma alimentação de 14 V CC foi fornecida. Em outras modalidades, fontes de tensão de CC menores (ou maiores) podem ser fornecidas. Nesse caso, uma razão de voltas de transformador maior (ou menor) pode ser fornecida para aumentar a tensão de carga para o nível desejado ou tensões operacionais menores podem ser usadas.
[00106] Na modalidade acima, o dispositivo médico foi disposto para aplicar uma potência desejada (sob a forma de energia ultrassônica ou energia elétrica) ao tecido/vaso preso pelo fórceps. Em uma modalidade alternativa, o dispositivo pode ser disposto para aplicar uma corrente desejada ou um nível de tensão desejado ao transdutor ultrassônico ou ao fórceps.
[00107] Na modalidade acima, a bateria é mostrada integralmente 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.
[00108] Na modalidade acima, um microprocessador com base no circuito de controle foi fornecido. Isso é preferível devido à facilidade com que o microprocessador pode ser programado para executar as ações de controle acima usando o software de computador adequado. Esse software pode ser fornecido em um meio tangível, como um CD- ROM ou similar. Alternativamente, o circuito de controle de hardware pode ser usado no lugar do microprocessador com base no circuito descrito acima.
[00109] Na modalidade acima, o usuário controlou se a energia liberada para o vaso/tecido era energia ultrassônica ou energia elétrica RF. Em modalidades alternativas, o microprocessador pode controlar a seleção com base em um sinal de controle gerado internamente ou em resposta a um sinal de controle recebido de um outro dispositivo.
[00110] Na modalidade acima, o circuito de fusível ativo abriu uma chave que desconectou o gerador de sinal de ponte das baterias. Em uma modalidade alternativa, o circuito de fusível ativo poderia, em vez disso, chavear em uma impedância grande entre as baterias e o gerador de sinal de ponte para limitar a corrente drenada das baterias. Além disso, a chave poderia ser usada para desconectar a alimentação de tensão positiva a partir do gerador de sinal em vez de desconectar o terminal negativo das baterias.
Claims (18)
1. Aparelho eletrônico para uso em um dispositivo médico (1) possuindo um transdutor ultrassônico (8) e um atuador de extremidade (7), o aparelho eletrônico que compreende: um circuito de acionamento para gerar um sinal de acionamento periódico; e um controlador (23) operável para controlar o circuito de acionamento; caracterizado pelo fato de que o circuito de acionamento compreende um primeiro circuito ressonante (43-1) possuindo uma primeira frequência de ressonância e um segundo circuito ressonante (43-2) possuindo uma segunda frequência de ressonância, que é diferente da primeira frequência de ressonância, e em que o controlador é operável para controlar o circuito de acionamento de modo que o circuito de acionamento gere um sinal de acionamento possuindo uma frequência correspondendo à primeira frequência de ressonância quando o sinal de acionamento deve ser aplicado ao transdutor ultrassônico, e de modo que o circuito de acionamento gere um sinal de acionamento possuindo uma frequência correspondendo à segunda frequência de ressonância quando o sinal de acionamento deve ser aplicado ao atuador de extremidade.
2. Dispositivo médico, caracterizado pelo fato de que compreende: um atuador de extremidade para prender um vaso/tecido; um transdutor ultrassônico acoplado ao atuador de extremidade; e o aparelho eletrônico como definido na reivindicação 1.
3. Dispositivo, de acordo com a reivindicação 2, caracterizado pelo fato de que a primeira frequência de ressonância corresponde a uma característica ressonante do transdutor ultrassônico.
4. Dispositivo, de acordo com a reivindicação 2, caracterizado pelo fato de que compreende um gerador de sinal acoplado entre o controlador e o circuito de acionamento para gerar uma tensão de variação cíclica de uma alimentação de tensão CC, dependendo de sinais de controle do controlador, e para fornecer a tensão de variação cíclica ao primeiro e ao segundo circuitos ressonantes do circuito de acionamento.
5. Dispositivo, de acordo com qualquer uma das reinvin- dicações 2 a 4, caracterizado pelo fato de que o controlador é disposto para variar o período do sinal de acionamento na primeira frequência de ressonância ou na segunda frequência de ressonância para variar a energia fornecida ao vaso ou tecido presos pelo atuador de extremidade.
6. Dispositivo, de acordo com a reivindicação 4, caracterizado pelo fato de que o controlador é configurado para variar o período do sinal de acionamento, de modo que a frequência do sinal de acionamento varie ao redor da primeira frequência de ressonância dentro de 0,1% a 1% da primeira frequência de ressonância, ou de modo que a frequência do sinal de acionamento varie ao redor da segunda frequência de ressonância dentro de 40% a 60% da segunda frequência de ressonância.
7. Dispositivo, de acordo com a reivindicação 4 ou 5, carac-terizado pelo fato de que as características de ressonância do primeiro e do segundo circuitos ressonantes variam com o tecido ou vaso preso pelo fórceps, e em que o controlador é configurado para variar o período do sinal de acionamento para rastrear alterações na respectiva característica de ressonância.
8. Dispositivo, de acordo com qualquer uma das reivindicações 2 a 6, caracterizado pelo fato de que ainda compreende um guia de ondas ultrassônicas acoplado ao transdutor ultrassônico para guiar energia ultrassônica gerada pelo transdutor ultrassônico em direção ao atuador de extremidade; em que o atuador de extremidade compreende primeira e segunda garras, e em que o segundo circuito ressonante é acoplado eletricamente às primeira e segunda garras do atuador de extremidade.
9. Dispositivo, de acordo com a reivindicação 7, caracterizado pelo fato de que a primeira garra do atuador de extremidade é acoplada eletricamente ao guia de ondas e em que o segundo circuito ressonante é acoplado eletricamente à primeira garra do atuador de extremidade através do guia de ondas ultrassônicas.
10. Dispositivo, de acordo com a reivindicação 7 ou 8, caracterizado pelo fato de que o primeiro circuito ressonante é acoplado eletricamente ao transdutor ultrassônico e ao guia de ondas.
11. Dispositivo, de acordo com qualquer uma das reivindicações 2 a 9, caracterizado pelo fato de que compreende um circuito de detecção (31, 33) para detectar um sinal de acionamento aplicado ao transdutor ultrassônico ou ao atuador de extremidade.
12. Dispositivo, de acordo com a reivindicação 11, caracterizado pelo fato de que um ou ambos dentre os primeiro e segundo circuitos ressonantes compreendem pelo menos um dentre uma bobina indutora (47), um capacitor (45) e um resistor e em que o circuito de detecção compreende um circuito amplificador operacional (AmpOp) (69-1, 69-2) para detectar a tensão ao longo da bobina indutora ou do capacitor ou do resistor e para converter a tensão detectada em um sinal de sensor adequado para entrar no controlador.
13. Dispositivo, de acordo com a reivindicação 11, caracterizado pelo fato de que um ou ambos dentre o primeiro e segundo circuitos ressonantes compreendem um elemento de impedância que é conectado entre o circuito ressonante e um potencial de referência e em que o circuito de detecção compreende um circuito divisor para obter uma medição da tensão ao longo do elemento de impedância e um gerador de sinal de polarização para aplicar um sinal de polarização CC à medição de tensão.
14. Dispositivo, de acordo com a reivindicação 13, caracterizado pelo fato de que o elemento de impedância compreende um capacitor ou um resistor.
15. Dispositivo, de acordo com a reivindicação 13 ou 14, caracterizado pelo fato de que o circuito de detecção compreende o circuito de bloqueamento de CC para evitar o acoplamento do sinal de polarização CC do gerador de sinal de polarização ao circuito de acionamento.
16. Dispositivo, de acordo com a reivindicação 13, 14 ou 15, caracterizado pelo fato de que o gerador do sinal de polarização compreende um circuito divisor de tensão conectado entre uma tensão de referência e uma tensão de alimentação do controlador.
17. Dispositivo, de acordo com qualquer uma das reivindicações 2 a 16, caracterizado pelo fato de que compreende uma ou mais baterias (15) para alimentar o dispositivo e ainda compreende um circuito de fusível ativo (130) para proteger a uma ou mais baterias.
18. Dispositivo, de acordo com a reivindicação 17, caracterizado pelo fato de que o circuito de fusível ativo compreende uma chave (139) acoplada eletricamente entre um terminal da uma ou mais baterias e o circuito de acionamento, e circuito de controle configurado para abrir a chave para isolar o terminal de alimentação do circuito de acionamento.
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EP3082627A1 (en) | 2016-10-26 |
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JP2017500940A (ja) | 2017-01-12 |
CN105992563B (zh) | 2021-03-19 |
JP6483130B2 (ja) | 2019-03-13 |
US20210186553A1 (en) | 2021-06-24 |
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Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 08/12/2014, OBSERVADAS AS CONDICOES LEGAIS. |