Apparatus and method for acoustic heat generation and hyperthermia

• US 5,501,655 A
• Filed: 07/15/1994
• Issued: 03/26/1996
• Est. Priority Date: 03/31/1992
• Status: Expired due to Fees

• Current Assignee: Massachusetts Institute of Technology
• Original Assignee: Massachusetts Institute of Technology
• Inventors: Rolt, Kenneth D., Lele, Padmakar P.
• Primary Examiner(s): Kamm, William E.
• Assistant Examiner(s): Casler, Brian L.
• Application Number:
  US08/275,809
• Time in Patent Office: 620 Days
• Field of Search: 601/2, 601/3, 128/660.03, 600/10, 607/96, 607/97, 607/154
• US Class Current: 601/3
• CPC Class Codes: A61B 2017/22028 arrays, e.g. phased arrays
• CPC Class Codes: A61N 2007/006 Lenses
• CPC Class Codes: A61N 2007/0073 using multiple frequencies
• CPC Class Codes: A61N 2007/0078 with multiple treatment transducers
• CPC Class Codes: A61N 2007/0095 by modifying an excitation signal
• CPC Class Codes: A61N 7/02 Localised ultrasound hyperthermia hyperthermia in general A61F7/00
• CPC Class Codes: G10K 15/02 Synthesis of acoustic waves synthesis of speech G10L13/00

Abstract

An ultrasound hyperthermia applicator suitable for medical hyperthermia treatment, and method for using the same, includes two ultrasound sources producing focused ultrasound beams of frequencies f₀ and f₁. An aiming device directs the two ultrasound beams so that they cross each other confocally at the target. A controller activates the two ultrasound sources so that the target is simultaneously irradiated by the two focused ultrasound beams. The two ultrasound sources provide acoustic energy sufficient to cause significant intermodulation products to be produced at the target due to the interaction of the two ultrasound beams. The intermodulation products are absorbed by the target to enhance heating of the target. In preferred embodiments the ultrasound sources include pair of signal generator for producing gated ultrasound output signals driving single crystal ultrasound transducers. In other embodiments the ultrasound sources include a pair of phased array ultrasound transducers for generating two steerable ultrasound beams. An aiming device is provided for electronically steering and focusing the two ultrasound beams so that they cross each other confocally at the target. Further embodiments employ pluralities of transducers, arrays, or both.

Claims

1. An ultrasound hyperthermia applicator for heating a tissue mass target within a human body, comprising

first ultrasound hyperthermia source means for producing ultrasound energy having a frequency f₀ between about 50 Khz and 5 Mhz;

first focusing means for focusing the energy from the first ultrasound hyperthermia source means and for producing a first focused ultrasound beam for heating the target;

second ultrasound hyperthermia source means for producing ultrasound energy having a frequency f₁ between about 50 Khz and 5 Mhz;

second focusing means for focusing the energy from the second ultrasound hyperthermia source means and for producing a second focused ultrasound beam for heating the target;

aiming means for directing the first and second focused ultrasound beams at the target to be heated so that the first and second ultrasound beams cross each other at the target, and the focus of the first and the second ultrasound beams are substantially coincident where the beams cross; and

control means for activating the first and second ultrasound hyperthermia source means to provide simultaneous irradiation of the target by each of the first and second focused ultrasound beams to heat the target;

wherein the first and second ultrasound hyperthermia source means provide ultrasound energy sufficient for producing intermodulation products at the target where the first and second focused ultrasound beams cross, and wherein the intermodulation products including integral multiples of sum-frequencies f₀ +f₁ which are absorbed by the target to provide additional heat to the target and the intermodulation products are absorbed by the tissue mass target at a substantially greater rate than ultrasound energy having a frequency of either f₀ or f₁ or a linear superposition of f₀ and f₁.

2. The apparatus of claim 1 wherein the first and second ultrasound hyperthermia source means produce ultrasound energies having substantially the same frequency.

3. The apparatus of claim 1 wherein the aiming means is adapted to direct the first and second beams at the tissue mass which is located within the cranium.

4. The apparatus of claim 1 wherein the first and second ultrasound hyperthermia source means produce ultrasound energies having substantially the same frequency.

5. The apparatus of claim 1 wherein the first ultrasound hyperthermia source means produces ultrasound energy which is a CW ultrasound signal having a frequency of f₀.

6. The apparatus of claim 1 wherein the first ultrasound hyperthermia source means produces ultrasound energy which is a bandlimited modulated signal having a center frequency of f₀.

7. The apparatus of claim 6 wherein the second ultrasound hyperthermia source means produces ultrasound energy which is a CW ultrasound signal having a frequency of f₁.

8. The apparatus of claim 6 wherein the second ultrasound hyperthermia source means produces ultrasound energy which is a bandlimited modulated ultrasound signal having a center frequency of f₁.

9. The apparatus of claim 1

wherein the first ultrasound hyperthermia source means comprises:

a first signal generator means for producing a first gated ultrasound output signal at frequency f₀ in response to an input control signal generated by the control means; and

a first power amplifier coupled to the output of the first signal generator means for amplifying the first gated ultrasound output signal;

the first focusing means comprises;

a first ultrasound transducer coupled to the first power amplifier for converting the first amplified gated ultrasound output signal into the first focused ultrasound beam;

the second ultrasound hyperthermia source means comprises;

a second signal generator means for producing a second gated ultrasound output signal at frequency f₁ in response to another input control signal generated by the control means;

a second power amplifier coupled to the output of the second signal generator means for amplifying the second gated ultrasound output signal; and

the second focusing means comprises;

a second ultrasound transducer coupled to the second power amplifier for converting the second amplifier gated ultrasound output signal into the second focused ultrasound beam.

10. The apparatus of claim 9, wherein each of the first and second ultrasound transducers comprises an acoustic lens for focusing its corresponding ultrasound beam at the target.

11. The apparatus of claim 10, wherein the aiming means comprises means for fixing the first and second ultrasound transducers relative to each other so that the first and second ultrasound beams cross each other at a predetermined angle, with coincident foci.

12. The apparatus of claim 9 wherein the first signal generator means produces the first gated ultrasound output signal which is a CW signal having a frequency of f₀.

13. The apparatus of claim 9 wherein the first signal generator means produces the first gated ultrasound output signal which is a bandlimited modulated signal having a center frequency f₀.

14. The apparatus of claim 13 wherein the second signal generator means produces the second gated ultrasound output signal which is a CW signal having a frequency f₁.

15. The apparatus of claim 13 wherein the second signal generator means produces the second gated ultrasound output signal which is a bandlimited modulated signal having a center frequency of f₁.

16. The apparatus of claim 1

wherein the first and second ultrasound hyperthermia source means produce ultrasound energies having substantially the same frequency,

wherein the first and second ultrasound hyperthermia source means comprise:

a signal generator means for producing a gated ultrasound signal at frequency f₀ and f₁ in response to an input control signal generated by the control means;

a power amplifier coupled to the output of the signal generator means for amplifying the gated ultrasound signal; and

a power splitter coupled to the output of the amplifier for dividing the amplified gated ultrasound signal between a first power splitter output and a second power splitter output;

wherein the first focusing means comprises a first ultrasound transducer coupled to the first power splitter output for converting the amplified gated ultrasound signal into the first focused ultrasound beam; and

wherein the second focusing means comprises a second ultrasound transducer coupled to the second power splitter output for converting the amplified gated ultrasound signal into the second focused ultrasound beam.

17. The apparatus of claim 16, wherein each of the first and second ultrasound transducers comprises an acoustic lens for focusing its corresponding ultrasound beam at the target.

18. The apparatus of claim 16, wherein the aiming means comprises means for fixing the first and second ultrasound transducers relative to each other so that the first and second ultrasound beams cross each other at a predetermined angle with coincident foci.

19. The apparatus of claim 16 wherein the signal generator means produces the gated ultrasound signal which is a CW signal having a frequency f₀.

20. The apparatus of claim 16 wherein the signal generator means produces the gated ultrasound signal which is a bandlimited modulated signal having a center frequency f₀.

21. The apparatus of claim 1, wherein

the first ultrasound source means comprises a first phased array ultrasound transducer coupled to a first ultrasound scanner for generating a first steerable ultrasound beam at frequency f₀ ;

the second ultrasound source means comprises a second phased array ultrasound transducer coupled to a second ultrasound scanner for generating a second steerable ultrasound beam at frequency f₁ ; and

the aiming means further comprises means for electronically steering the first and second ultrasound beams.

22. The apparatus of claim 21, wherein each of the first and second ultrasound scanners comprises means for electronically focusing its corresponding ultrasound beam at the target.

23. The apparatus of claim 21, wherein the aiming means comprises means for fixing the first and second phased array ultrasound transducers relative to each other so that the first and second ultrasound beams can be electronically steered to cross each other at a predetermined angle with coincident foci.

24. The apparatus of claim 21 wherein the first ultrasound source means produces a CW ultrasound signal having a frequency of f₀.

25. The apparatus of claim 21 wherein the first ultrasound source means produces a bandlimited modulated signal having a center frequency of f₀.

26. The apparatus of claim 25 wherein the second ultrasound source means produces a CW ultrasound signal having a frequency of f₁.

27. The apparatus of claim 25 wherein the second ultrasound source produces a bandlimited modulated ultrasound signal having a center frequency of f₁.

28. A method for heating a target with ultrasound, comprising the steps of

producing a first focused ultrasound beam having a frequency f₀ between about 50 kHz and 5 MHz with a first ultrasound hyperthermia source;

producing a second focused ultrasound beam having a frequency f₁ between about 50 kHz and 5 MHz with a second ultrasound hyperthermia source;

directing the first and second focused ultrasound beams at the target to be heated so that the first and second ultrasound beams cross each other at the target, and the focus of the first and second ultrasound beams are substantially coincident where the beams cross;

wherein

the first and second ultrasonic beams have sufficient ultrasound energy to produce intermodulation products at the target where the first and second ultrasound beams cross, and wherein the intermodulation products include integral multiples of sum-frequencies f₀ +f₁ which are absorbed by the target to provide additional heat to the target and the intermodulation products are highly absorbed by the target at a substantially greater rate than ultrasound energy having a frequency of either f₀ or f₁ or a linear superposition of f₀ and f₁.

29. The method of claim 28, wherein frequency f₀ is substantially the same as frequency f₁.

30. The method of claim 28 wherein the directing step further comprises directing the ultrasound beams at a tissue mass located within a human cranium.

31. The method of claim 28, further comprising the step of fixing the first and second ultrasound sources relative to each other so that the first and second ultrasound beams cross each other at a predetermined angle with coincident foci.

32. The method of claim 28 wherein the first ultrasound source produces a CW ultrasound signal having a frequency of f₀.

33. The method of claim 28 wherein the first ultrasound source produces a bandlimited modulated signal having a center frequency of f₀.

34. The method of claim 33 wherein the second ultrasound source produces a CW ultrasound signal having a frequency of f₁.

35. The method of claim 33 wherein the second ultrasound source produces a bandlimited modulated ultrasound signal having a center frequency of f₁.

36. The method of claim 28, wherein

producing the first ultrasound beam comprises providing a first phased array ultrasound transducer coupled to a first ultrasound scanner for generating a first steerable ultrasound beam at frequency f₀ ;

producing the second ultrasound beam comprises providing a second phased array ultrasound transducer coupled to a second ultrasound scanner for generating a second steerable ultrasound beam at frequency f₁ ; and

directing the first and second ultrasound beams comprises electronically steering the first and second ultrasound beams.

37. The method of claim 36, further comprising the step of electronically focusing the first and second ultrasound beams at the target.

38. The apparatus of claim 36, wherein the directing step further comprises the steps of

fixing the first and second phased array ultrasound transducers relative to each other, and

electronically steering the first and second ultrasound beams to cross each other at a predetermined angle with coincident foci.

39. An ultrasound hyperthermia applicator for heating a target, comprising

a plurality of N ultrasound hyperthermia source means which each produces an ultrasound energy having a corresponding frequency f_n between about 50 kHz and 5 MHz, where n is from 1 to N;

a plurality of focusing means which each focuses the energy from a different one of the hyperthermia source means and produces one of N focused ultrasound beams for heating the target;

aiming means for directing the N focused ultrasound beams at the target to be heated so that the N ultrasound beams cross each other at the target, and the focus of each of the N ultrasound beams are substantially coincident where the beams cross; and

control means for activating the N ultrasound hyperthermia source means to provide simultaneous irradiation of the target by each of the N focused ultrasound beams to heat the target;

wherein the N ultrasound hyperthermia source means provide sufficient ultrasound energy for producing intermodulation products at the target where the N ultrasound beams cross, and wherein the intermodulation products include integral multiples of sum frequencies of the corresponding frequencies f_n which are absorbed by the target to provide additional heat to the target and the intermodulation products are highly absorbed by the target at a substantially ultrasound energy having a frequency of of f_n or a linear superposition of f_n.

40. The apparatus of claim 39 wherein the plurality of N ultrasound hyperthermia source means produce ultrasound energies having substantially the same frequency.

41. An ultrasound hyperthermia applicator for heating a target, comprising

first ultrasound hyperthermia source means for producing ultrasound energy having a frequency f₀ between about 50 Khz and 5 Mhz;

first focusing means for focusing the energy from the first ultrasound hyperthermia source means and for producing a first focused ultrasound beam for heating the target;

second ultrasound hyperthermia source means for producing ultrasound energy having a frequency f₁ between about 50 Khz and 5 Mhz;

second focusing means for focusing the energy from the second ultrasound hyperthermia source means and for producing a second focused ultrasound beam for heating the target;

aiming means for directing the first and second focused ultrasound beams at the target to be heated so that the first and second ultrasound beams cross each other at a plurality of selectable points within a three-dimensional region which includes the target, and the focus of the first and the second ultrasound beams are substantially coincident at the plurality of selectable points where the beams cross; and

control means for activating the first and second ultrasound hyperthermia source means to provide simultaneous irradiation of the target by each of the first and second focused ultrasound beams to heat the target at the plurality of selectable points;

wherein the first and second ultrasound hyperthermia source means provide sufficient ultrasound energy for producing intermodulation products at the plurality of selectable points where the first and second focused ultrasound beams cross, and wherein the intermodulation products include integral multiples of sum-frequencies f₀ +f₁ which are absorbed by the target at the plurality of selectable points to provide additional heat to the target and the intermodulation products are highly absorbed by the target at a substantially greater rate than ultrasound energy having a frequency of either f₀ or f₁ or a linear superposition of f₀ and f₁.

42. An ultrasound hyperthermia applicator for heating a target, comprising

first ultrasound hyperthermia source means for producing ultrasound energy which is a triangular wave broadband signal rich in harmonics of a fundamental frequency f₀ between about 50 Khz and 5 Mhz;

first focusing means for focusing the energy from the first ultrasound hyperthermia source means and for producing a first focused ultrasound beam for heating the target;

second ultrasound hyperthermia source means for producing ultrasound energy which is a triangular wave broadband signal rich in harmonics of a fundamental frequency f₁ ;

second focusing means for focusing the energy from the second ultrasound hyperthermia source means and for producing a second focused ultrasound beam for heating the target;

aiming means for directing the first and second focused ultrasound beams at the target to be heated so that the first and second ultrasound beams cross each other at the target, and the focus of the first and the second ultrasound beams are substantially coincident where the beams cross; and

control means for activating the first and second ultrasound hyperthermia source means to provide simultaneous irradiation of the target by each of the first and second focused ultrasound beams to heat the target;

wherein the first and second ultrasound hyperthermia source means and provide broadband signals which are rich in harmonics for producing a similarly rich variety of intermodulation products at the target where the first and second focused ultrasound beams cross, and wherein the intermodulation products include integral multiples of sum-frequencies f₀ +f₁ which are easily absorbed by the target to provide additional heat to the target and the intermodulation products are highly absorbed by the target at a substantially greater rate than ultrasound energy having a frequency of either f₀ or f₁ or a linear superposition of f₀ and f₁.

43. An ultrasound hyperthermia applicator for heating a target, comprising

first ultrasound hyperthermia source means for producing ultrasound energy having a frequency f₀ between about 50 Khz and 5 Mhz;

first focusing means for focusing the energy from the first ultrasound hyperthermia source means and for producing a first focused main ultrasound beam for heating the target;

second ultrasound hyperthermia source means for producing ultrasound energy having a frequency f₁ between about 50 Khz and 5 Mhz;

second focusing means for focusing the energy from the second ultrasound hyperthermia source means and for producing a second focused main ultrasound beam for heating the target;

aiming means for directing the first and second focused main ultrasound beams at the target to be heated so that the first and second main ultrasound beams cross each other at the target, and the focus of the first and the second main ultrasound beams are substantially coincident where the main beams cross; and

control means for activating the first and second ultrasound hyperthermia source means to provide simultaneous irradiation of the target by each of the first and second focused main ultrasound beams to heat the target;

wherein the first and second ultrasound hyperthermia source means provide ultrasound energy sufficient for producing intermodulation products at the target where the first and second focused main ultrasound beams cross, and wherein the intermodulation products include integral multiples of sum-frequencies f₀ +f₁ which are absorbed by the target to provide additional heat to the target and the intermodulation products are highly absorbed by the target at a substantially greater rate than ultrasound energy having a frequency of either f₀ or f₁ or a linear superposition of f₀ and f₁.

44. An ultrasound hyperthermia applicator for heating a target, comprising

first ultrasound hyperthermia source means for producing ultrasound energy which is a modulated signal centered about a frequency f₀ between about 50 Khz and 5 Mhz, wherein the modulation is in the form of amplitude modulation, frequency modulation, or pseudo-random modulation;

first focusing means for focusing the energy from the first ultrasound hyperthermia source means and for producing a first focused ultrasound beam for heating the target;

second ultrasound hyperthermia source means for producing ultrasound energy which is a modulated signal centered about a frequency f₁ between about 50 Khz and 5 Mhz, wherein the modulation is in the form of amplitude modulation, frequency modulation, or pseudo-random modulation;

second focusing means for focusing the energy from the second ultrasound hyperthermia source means and for producing a second focused ultrasound beam for heating the target;

aiming means for directing the first and second focused ultrasound beams at the target to be heated so that the first and second ultrasound beams cross each other at the target, and the focus of the first and the second ultrasound beams are substantially coincident where the beams cross; and

control means for activating the first and second ultrasound hyperthermia source means to provide simultaneous irradiation of the target by each of the first and second focused ultrasound beams to heat the target;

wherein the first and second ultrasound hyperthermia source means provide and ultrasound energy sufficient for producing intermodulation products at the target where the first and second focused ultrasound beams cross, and wherein the intermodulation products include integral multiples of sum-frequencies f₀ +f₁ which are absorbed by the target to provide additional heat to the target and the intermodulation products are highly absorbed by the target at a substantially greater rate than ultrasound energy having a frequency of either f₀ or f₁ or a linear superposition of f₀ and f₁.