WO2013094170A1

WO2013094170A1 - Photoacoustic imaging method and apparatus

Info

Publication number: WO2013094170A1
Application number: PCT/JP2012/008034
Authority: WO
Inventors: 覚入澤
Original assignee: 富士フイルム株式会社
Priority date: 2011-12-22
Filing date: 2012-12-17
Publication date: 2013-06-27
Also published as: JP2013128722A

Abstract

[Problem] To enable a photoacoustic imaging method to display an image reflecting a diagnostic characteristic that is being sought from the displayed image such as imaging depth, definition, etc. [Solution] A photoacoustic imaging apparatus, which has a means for emitting pulsed light toward a test object and detecting the acoustic waves generated from the test object as a result thereof to generate photoacoustic data, is provided with: a condition-inputting means, which inputs the diagnostic characteristic that is being sought from the displayed image and/or information representing the band of the acoustic wave-detecting means; and a pulse width-adjusting means for adjusting the pulse width of the pulsed light on the basis of the information input from the condition-inputting means.

Description

Photoacoustic imaging method and apparatus

The present invention relates to a photoacoustic imaging method, that is, a method for imaging a subject based on an acoustic wave generated from the subject along with the emission of light toward the subject such as a living tissue.

The present invention also relates to an apparatus for performing a photoacoustic imaging method.

Conventionally, as shown in Patent Documents 1 and 2 and Non-Patent Document 1, for example, photoacoustic imaging apparatuses that image the inside of a living body using a photoacoustic effect are known. In this photoacoustic imaging apparatus, for example, pulsed light such as pulsed laser light is emitted toward a living body. Inside the living body that has received the pulsed light, the living tissue that has absorbed the energy of the pulsed light undergoes volume expansion due to heat, and generates an acoustic wave. Therefore, it is possible to detect this acoustic wave with a detection means such as an ultrasonic probe and to visualize the inside of the living body based on the electrical signal (photoacoustic signal) obtained thereby.

Since the photoacoustic imaging apparatus constructs an image based only on the acoustic wave radiated from a specific absorber, it is suitable for imaging a specific tissue in a living body, such as a blood vessel. It has become.

JP 2005-21380 A Special table 2010-512929

A High-Speed Photoacoustic Tomography System based on a Commercial Ultrasound and a Custom Transducer Array, X. Wang, J. Cannata, D. DeBusschere, C. Hu, JBFowlkes, and P. Carson, Proc.SPIE, Vol. 7564, 756424 (Feb.23, 2010)

According to the photoacoustic imaging method, as described above, it is possible to image a tissue that has entered from the surface of the subject, such as a blood vessel of a living body, but in clinical or medical research, There is a need for a particularly clear image of tissue present at a predetermined depth from the surface. There is also a demand for imaging a tissue existing at a certain depth from the surface of the subject with particularly high definition.

However, the conventional photoacoustic imaging apparatus cannot sufficiently cope with the diagnostic characteristics required for a display image, such as the depth and definition that can be clearly imaged as described above.

The present invention has been made in view of the above circumstances, and an object thereof is to provide a photoacoustic imaging method capable of displaying an image sufficiently corresponding to a required diagnostic characteristic.

It is another object of the present invention to provide a photoacoustic imaging apparatus that can implement such a photoacoustic imaging method.

The photoacoustic imaging method according to the present invention comprises:
As described above, a pulsed light having a wavelength that is absorbed inside the subject is emitted, and the acoustic wave emitted from the subject is detected by the acoustic wave detecting means to obtain photoacoustic data. In the photoacoustic imaging method of imaging the subject based on photoacoustic data and displaying it on the image display means,
The pulse width of the pulsed light is adjusted according to the diagnostic characteristics required for the displayed image and / or the band of the acoustic wave detecting means.

Note that the above-mentioned diagnostic characteristics relate to, for example, the depth from the subject surface of the tissue desired to be imaged and the image definition.

When the diagnostic characteristics are related to the depth and the image definition, it is desirable to set the pulse width larger as the depth from the subject surface of the tissue to be imaged is larger.

Further, when the diagnostic characteristics are related to the depth and the image definition, it is preferable to set the pulse width to be smaller as the image definition is higher.

Moreover, in the photoacoustic imaging method of this invention, you may make it set the said pulse width smaller, so that the said zone | band is high.

On the other hand, the photoacoustic imager according to the present invention is:
As described above, a pulsed light having a wavelength that is absorbed inside the subject is emitted, and the acoustic wave emitted from the subject is detected by the acoustic wave detecting means to obtain photoacoustic data. In the photoacoustic imaging apparatus that images the subject based on photoacoustic data and displays the image on the image display means,
Condition input means for inputting information indicating diagnostic characteristics required for the displayed image and / or a band of the acoustic wave detection means;
And pulse width adjusting means for adjusting the pulse width of the pulsed light based on information input from the condition input means.

The condition input means preferably inputs the depth of the tissue desired to be imaged from the subject surface and the image definition as diagnostic characteristics.

When the condition input means inputs the depth and the image definition, the pulse width adjustment means increases the pulse width as the depth from the subject surface of the tissue to be imaged increases. It is desirable to be configured to set a larger value.

Further, when the condition input means inputs the depth and the image definition, the pulse width adjusting means is configured to set the pulse width smaller as the image definition is higher. Is also desirable.

The pulse width adjusting means may be configured to set the pulse width smaller as the band of the acoustic wave detecting means is higher.

The acoustic wave detecting means in the photoacoustic imaging apparatus of the present invention may be either or both of a probe that detects acoustic waves and an electric circuit that processes an output signal from the probe. . Therefore, the information indicating the band input to the condition input unit may indicate the band of the probe or may indicate the band of the electric circuit.

The probe as described above is often detachable from the photoacoustic imaging apparatus main body. As such, when at least a part of the acoustic wave detection means is detachable from the photoacoustic imaging apparatus main body, when the detachable part is attached to the photoacoustic imaging apparatus main body. It is desirable that information indicating its own band is automatically input to the condition input means.

Further, the photoacoustic imaging apparatus of the present invention is a photodifferential waveform inverse convolution that generates, from photoacoustic data, a signal obtained by deconvolution of a photodifferential waveform that is a differential waveform of a time waveform of the light intensity of pulsed light received by a subject. Incorporating means may be provided.

According to the photoacoustic imaging method of the present invention, the pulse width of the pulsed light is adjusted according to the diagnostic characteristics required for the displayed image and / or the band of the acoustic wave detection means. In consideration of this band, it is possible to display a photoacoustic image sufficiently corresponding to the required diagnostic characteristics.

On the other hand, according to the photoacoustic imaging apparatus of the present invention, condition input means for inputting diagnostic characteristics required for the displayed image and / or information indicating the band of the acoustic wave detection means, and input from the condition input means. Since the pulse width adjusting means for adjusting the pulse width of the pulsed light based on the information is provided, the above-described photoacoustic imaging method according to the present invention can be implemented.

In the photoacoustic imaging apparatus of the present invention, in particular, the portion of the acoustic wave detecting means that is detachable from the photoacoustic imaging apparatus main body has its own band when attached to the photoacoustic imaging apparatus main body. When the information to be indicated is automatically input to the condition input means, it is not necessary for the apparatus user to input the information indicating the band, and the operation for photoacoustic imaging is simplified.

The block diagram which shows schematic structure of the photoacoustic imaging device by one Embodiment of this invention. The block diagram which shows the partial structure of the photoacoustic imaging device by another embodiment of this invention.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. FIG. 1 is a block diagram showing a basic configuration of a photoacoustic imaging apparatus 10 according to an embodiment of the present invention. This photoacoustic imaging apparatus 10 can acquire both a photoacoustic image and an ultrasonic image as an example. An ultrasonic probe (probe) 11, an ultrasonic unit 12, a laser light source unit 13, an image The display unit 14, the condition input operation unit 50, the condition input control unit 51, and the pulse width adjustment unit 52 are provided.

The laser light source unit 13 emits laser light having a center wavelength of 756 nm, for example. The subject is irradiated with the laser beam emitted from the laser light source unit 13. The laser light is preferably guided to the probe 11 using light guide means such as a plurality of optical fibers and emitted from the probe 11 toward the subject.

The probe 11 performs output (transmission) of ultrasonic waves to the subject and detection (reception) of reflected ultrasonic waves reflected back from the subject. For this purpose, the probe 11 has, for example, a plurality of ultrasonic transducers arranged one-dimensionally. The probe 11 detects ultrasonic waves (acoustic waves) generated by the observation object in the subject absorbing the laser light from the laser light source unit 13 by using the plurality of ultrasonic transducers. The probe 11 detects the acoustic wave and outputs an acoustic wave detection signal, and also detects the reflected ultrasonic wave and outputs an ultrasonic detection signal.

When the above-described light guide means is coupled to the probe 11, the end portion of the light guide means, that is, the tip portions of the plurality of optical fibers, are arranged along the arrangement direction of the plurality of ultrasonic transducers. From there, laser light is emitted toward the subject. Hereinafter, the case where the light guide means is coupled to the probe 11 as described above will be described as an example.

The light guiding means connected to the probe 11 is detachable from a photoacoustic imaging apparatus main body (not shown) that houses the ultrasonic unit 12 and the laser light source unit 13. Thereby, the probe 11 is detachable from the photoacoustic imaging apparatus main body. The base end of the light guide means may be fixed to the photoacoustic imaging apparatus main body, while the probe 11 may be configured to be detachable at the distal end. In this case, the probe 11 is eventually photoacoustic imaging. It becomes detachable from the apparatus main body.

When acquiring a photoacoustic image or an ultrasonic image of the subject, the probe 11 is moved in a direction substantially perpendicular to the one-dimensional direction in which the plurality of ultrasonic transducers are arranged. Two-dimensional scanning is performed by sound waves. This scanning may be performed by an inspector moving the probe 11 manually, or a more precise two-dimensional scanning may be realized using a scanning mechanism.

The ultrasonic unit 12 includes a reception circuit 21, an AD conversion unit 22, a reception memory 23, a data separation unit 24, an image reconstruction unit 25, a detection / logarithmic conversion unit 26, and an image construction unit 27. The output of the image construction unit 27 is input to the image display unit 14 including, for example, a CRT or a liquid crystal display device. Further, the ultrasonic unit 12 includes a transmission control circuit 30 and a control unit 31 that controls the operation of each unit in the ultrasonic unit 12.

The receiving circuit 21 receives the acoustic wave detection signal and the ultrasonic wave detection signal output from the probe 11. The AD conversion means 22 is a sampling means, which samples the acoustic wave detection signal and the ultrasonic detection signal received by the receiving circuit 21 and converts them into photoacoustic data and ultrasonic data, which are digital signals, respectively. This sampling is performed at a predetermined sampling period in synchronization with, for example, an externally input AD clock signal.

The laser light source unit 13 includes a Q switch pulse laser 32 made of a Ti: Sapphire laser, an alexandrite laser, or the like, and a flash lamp 33 that is an excitation light source. The laser light source unit 13 is supplied with a light trigger signal for instructing light emission from the control means 31. When the light trigger signal is received, the flash lamp 33 is turned on and the Q switch pulse laser is turned on. 32 is excited. For example, when the flash lamp 33 sufficiently excites the Q switch pulse laser 32, the control means 31 outputs a Q switch trigger signal. When receiving the Q switch trigger signal, the Q switch pulse laser 32 turns on the Q switch and emits a pulse laser beam having a wavelength of 756 nm.

Here, the time required from when the flash lamp 33 is turned on until the Q-switch pulse laser 33 is sufficiently excited can be estimated from the characteristics of the Q-switch pulse laser 33 and the like. In place of controlling the Q switch from the control means 31 as described above, the Q switch may be turned on after the Q switch pulse laser 32 is sufficiently excited in the laser light source unit 13. In that case, a signal indicating that the Q switch is turned on may be notified to the ultrasonic unit 12 side.

In the photoacoustic imaging apparatus of the present invention, a pulse laser capable of switching wavelengths may be used. When changing the pulse width of the pulse laser beam as will be described later, when the pulse laser can switch the wavelength, the pulse width is independently adjusted for the pulse laser of each wavelength. In general, the pulse width also changes depending on the wavelength. For example, in the case of a titanium sapphire laser, when the wavelength is shortened to about 700 nm, the pulse width becomes longer than the pulse width when the wavelength is about 800 nm (the relationship between the pulse width and the wavelength depends on the laser crystal). The degree of adjustment of the pulse width may be changed according to the wavelength so that the pulse laser beam of each wavelength matches the band of the probe.

The control unit 31 inputs an ultrasonic trigger signal for instructing ultrasonic transmission to the transmission control circuit 30. When receiving the ultrasonic trigger signal, the transmission control circuit 30 transmits an ultrasonic wave from the probe 11. The control means 31 outputs the optical trigger signal first, and then outputs an ultrasonic trigger signal. The output of the optical trigger signal outputs laser light to the subject and the detection of the acoustic wave, and then the output of the ultrasonic trigger signal outputs ultrasonic waves to the subject, and the reflected ultrasound. Is detected.

The control means 31 further outputs a sampling trigger signal that instructs the AD conversion means 22 to start sampling. The sampling trigger signal is output after the optical trigger signal is output and before the ultrasonic trigger signal is output, more preferably at the timing when the subject is actually irradiated with the laser light. Therefore, the sampling trigger signal is output in synchronization with the timing at which the control means 31 outputs the Q switch trigger signal, for example. When receiving the sampling trigger signal, the AD conversion means 22 starts sampling the acoustic wave detection signal output from the probe 11 and received by the receiving circuit 21.

After outputting the optical trigger signal, the control means 31 outputs the ultrasonic trigger signal at the timing when the detection of the acoustic wave is finished. At this time, the AD conversion means 22 continues the sampling without interrupting the sampling of the acoustic wave detection signal. In other words, the control unit 31 outputs the ultrasonic trigger signal in a state where the AD conversion unit 22 continues sampling the acoustic wave detection signal. When the probe 11 transmits ultrasonic waves in response to the ultrasonic trigger signal, the detection target of the probe 11 changes from acoustic waves to reflected ultrasonic waves. The AD conversion unit 22 continuously samples the acoustic wave detection signal and the ultrasonic wave detection signal by continuously sampling the detected ultrasonic wave detection signal.

The AD conversion unit 22 stores photoacoustic data and ultrasonic data obtained by sampling in a common reception memory 23. The sampling data stored in the reception memory 23 is photoacoustic data up to a certain point, and becomes ultrasonic data from a certain point. The data separation unit 24 separates the photoacoustic data and the ultrasonic data stored in the reception memory 23.

The condition input operation unit 50 includes means such as a keyboard and a mouse. The condition input operation unit 50 is operated by a user of the apparatus and inputs information on diagnostic characteristics to be described later to the condition input control unit 51. The condition input control unit 51 constitutes the condition input means in the present invention together with the condition input operation unit 50, and information indicating the probe's own band output from the probe 11 is also automatically input thereto. ing. The condition input control unit 51 inputs information indicating the band of the probe and information regarding diagnostic characteristics to the pulse width adjusting unit 52. The pulse width adjusting means 52 changes the pulse width of the pulse laser beam output from the laser 33 by changing the change speed of the drive voltage of an EO (electro-optic) element constituting the Q switch of the Q switch pulse laser 33, for example. Change.

In addition, when it is desired to change the pulse width further larger than the change width of the pulse width thus changed, an optical shutter may be added after the pulse laser 33 to control the pulse width. That is, such an optical shutter changes the pulse width of the pulse laser beam emitted from the incident pulse laser beam by shielding the incident pulse laser beam for a part of the emission time. Note that the partial time is, for example, from the start of the emission of the pulsed laser light to the time when the light intensity reaches the maximum value or the time before that.

As such an optical shutter, for example, an EO shutter in which an EO (Electrical-optical) element, a polarizing plate, and a drive circuit for the EO element are combined can be used. Alternatively, an optical system that splits the pulse laser beam, arranges an EO element on one optical path, changes the phase, and multiplexes them again can be used as a Mach-Zehnder light intensity modulator. it can.

Hereinafter, generation and display of a photoacoustic image will be described. The data separation unit 24 in FIG. 1 receives ultrasonic data read from the reception memory 23 and photoacoustic data obtained by irradiating the subject with pulsed laser light having a wavelength of 756 nm. The data separation unit 24 inputs only the photoacoustic data to the subsequent image reconstruction unit 25 when generating the photoacoustic image. The image reconstruction means 25 reconstructs data indicating a photoacoustic image based on the photoacoustic data.

The detection / logarithm conversion means 26 generates an envelope of data indicating the photoacoustic image, and then logarithmically converts the envelope to widen the dynamic range. The detection / logarithm conversion means 26 inputs these processed data to the image construction means 27. Based on the input data, the image construction unit 27 constructs a photoacoustic image related to the cross section scanned by the pulse laser beam, and inputs data indicating the photoacoustic image to the image display unit 14. Thereby, the photoacoustic image regarding the said cross section is displayed on the image display means 14. FIG.

As described above, the probe 11 is moved to scan the subject two-dimensionally with laser light, and a desired part of the subject, such as a blood vessel, is detected based on the image data regarding a plurality of cross sections obtained by the scanning. It is also possible to generate and display a photoacoustic image for three-dimensional display.

It is also possible to generate and display an ultrasonic image of the subject based on the ultrasonic data separated by the data separation means 24. The generation and display of the ultrasonic image may be performed by a conventionally known method, and since it is not directly related to the present invention, a detailed description is omitted, but such an ultrasonic image and a photoacoustic image are superimposed. It can also be displayed.

Next, the point of adjusting the pulse width of the pulsed laser beam emitted toward the subject will be described in detail. In the present embodiment, there are four diagnostic characteristics (1) to (4) shown in Table 1 below, and one probe band is set for one diagnostic characteristic. It has come to be.

The above (1) to (3) define the depth of the tissue to be displayed from the subject surface and the image definition as diagnostic characteristics, and (4) shows the output from the image construction means 27 as the diagnostic characteristics. It defines that the data indicating the photoacoustic image to be adapted is suitable for waveform analysis. In the present invention, as in the case of (4) above, the diagnostic characteristics required for the data indicating the photoacoustic image are also included in the “diagnostic characteristics required for the displayed image”.

In the present embodiment, by operating the condition input operation unit 50 of FIG. 1, the depth and image definition of the tissue to be displayed from the subject surface are input. More specifically, in this example, a unique mode name is set for each of the diagnostic characteristics (1) to (4), and the user of the apparatus simply inputs the mode name from the condition input operation unit 50. Input operation is finished. However, the present invention is not limited to this, and a desired diagnostic characteristic may be specifically input from a keyboard or the like each time the apparatus user uses the apparatus.

Further, since the information indicating the band of the probe 11 is automatically input from the probe 11 as described above, it is not necessary for the apparatus user to input the band information of the probe, and the work is simplified. However, the present invention is not limited to this, and the apparatus user may input the probe band information by operating the condition input operation unit 50.

Hereinafter, the reason for setting the pulse width in each of the above cases (1) to (4) will be described.

(1)
When it is desired to clearly observe a tissue existing in a relatively deep place of about 20 to 40 mm from the subject surface, it is advantageous to set the pulse width relatively large and increase the energy of the pulse laser beam. Also, when observing deep tissue, the frequency of the acoustic wave is lower because the photoacoustic wave becomes a signal containing many low frequency components and also from the point of acoustic absorption of the living body. Is advantageous. From this point of view, in this case, for example, a PZT (lead zirconate titanate) narrow band probe in a relatively low frequency band (center frequency: 3 MHz) is applied, and the pulse width is 50 ns. A relatively large value in the range of (nanosecond) to 100 ns or less is set. In this case, the pulse width may be set to 100 ns or more. The narrowband probe here is a probe in which the difference between the frequency higher and lower than the center frequency, which is half the sensitivity of the center frequency, is in the band of about 50% to 100% of the value of the center frequency.

(2)
If you want to clearly observe the tissue that exists at a medium depth of about 10 mm to less than 20 mm from the surface of the subject, set the pulse width slightly smaller than the above to slightly reduce the energy of the pulse laser beam. Is preferable for increasing the image definition. From this point of view, in this case, a PZT narrowband probe with a slightly higher frequency band (center frequency: 5 MHz) is applied, and the pulse width is set to a medium value in the range of 20 ns to less than 50 ns. Like to do.

(3)
If you want to clearly observe tissue existing in a shallow area of 0 to 10 mm or less from the surface of the subject, it is better to set the pulse width smaller than the above to make the energy of the pulse laser light smaller. It is preferable for displaying a simple image. From this point of view, in this case, a PZT narrowband probe of a higher frequency band (center frequency: 10 MHz) than the above is applied, and the pulse width is in the range of 10 ns to less than 20 ns, which is a slightly small value. It is set to.

(4)
In order to analyze and diagnose the waveform of the data indicating the photoacoustic image output from the detection / logarithm conversion means 26 instead of displaying an image, the pulse width can be minimized and the waveform details can be grasped. It is advantageous to do so. From this point of view, in this case, a PVDF (polyvinylidene difluoride) type broadband probe that can obtain even higher frequencies than the above is applied, and the pulse width is set to a small value in the range of 3 ns to less than 10 ns. I am doing so.

As described above, in the present embodiment, it is possible to display a photoacoustic image sufficiently corresponding to a required diagnostic characteristic.

Since the energy of the pulse laser beam decreases as the pulse width decreases, the excitation energy of the flash lamp 33 described above may be set higher to compensate for the decrease.

In the embodiment described above, the pulse width of the pulse laser beam is adjusted according to the band of the probe 11, but in addition to this, according to the band of the electric circuit that processes the output of the probe 11, Furthermore, the pulse width of the pulse laser beam may be adjusted according to the band of the probe 11 and the band of the electric circuit. Further, for example, when the band of the probe 11 is narrow, the band of the electric circuit may be changed according to the band of the probe 11 such as narrowing the band of the electric circuit.

Further, in the embodiment described above, an ultrasonic wave is used as an acoustic wave to be applied to the subject. However, this acoustic wave is not limited to the ultrasonic wave, and is appropriate depending on the test object, measurement conditions, and the like. As long as the frequency is selected, an acoustic wave in the audible frequency range may be used.

In addition, the photoacoustic imaging apparatus and method of the present invention are not limited to the above embodiment, and various modifications and changes made from the configuration of the above embodiment are also included in the scope of the present invention.

For example, the present invention can also be applied to a photoacoustic imaging apparatus and method in which a deconvolution process is performed. FIG. 2 is a block diagram showing a part of the photoacoustic imaging apparatus configured to perform the deconvolution processing. 2 is inserted, for example, between the image reconstruction means 25 and the detection / logarithmic conversion means 26 shown in FIG. 1, and is connected to the optical differential waveform deconvolution means 40 and its subsequent stage. Correction means 46. The split waveform deconvolution means 40 includes Fourier transform means 41 and 42, an inverse filter calculation means 43, a filter application means 44, and a Fourier inverse transform means 45.

The partial waveform deconvolution means 40 deconstructs an optical pulse differential waveform obtained by differentiating the time waveform of the light intensity of the pulsed laser light irradiated to the subject from the data indicating the photoacoustic image output from the image reconstruction means 25. Volute. By this deconvolution, photoacoustic image data showing an absorption distribution is obtained.

Hereinafter, this deconvolution will be described in detail. The Fourier transform means (first Fourier transform means) 41 of the optical differential waveform deconvolution means 40 converts the reconstructed photoacoustic image data from a time domain signal to a frequency domain signal by discrete Fourier transform. . The Fourier transform means (second Fourier transform means) 42 converts a signal obtained by sampling the optical pulse differential waveform at a predetermined sampling rate from a time domain signal to a frequency domain signal by discrete Fourier transform. For example, FFT can be used as the Fourier transform algorithm.

In the present embodiment, it is assumed that the sampling rate of the acoustic wave detection signal in the AD conversion means 22 is equal to the sampling rate of the optical pulse differential waveform. For example, the acoustic wave detection signal is sampled in synchronization with a sampling clock of Fs = 40 MHz, and the optical differential pulse is also sampled at a sampling rate of Fs_h = 40 MHz. The Fourier transform unit 41 Fourier transforms the photoacoustic image data output from the image reconstruction unit 25 obtained as a result of sampling at 40 MHz, for example, by 1024 points of Fourier transform. Further, the Fourier transform means 42 performs Fourier transform on the optical pulse differential waveform sampled at 40 MHz by 1024 points of Fourier transform.

The inverse filter calculation unit 43 obtains the inverse of the Fourier transformed optical pulse differential waveform as an inverse filter. For example, the inverse filter calculation means 43 obtains conj (fft_h) / abs (fft_h) ² as an inverse filter, where fft_h is a signal obtained by Fourier transforming the optical pulse differential waveform h. The filter applying unit 44 applies the inverse filter obtained by the inverse filter calculating unit 43 to the photoacoustic image data Fourier-transformed by the Fourier transform unit 41. For example, the filter application unit 44 multiplies the Fourier coefficient of the photoacoustic image data by the Fourier coefficient of the inverse filter for each element. By applying the inverse filter, the optical pulse differential waveform is deconvolved in the frequency domain signal. The Fourier inverse transform unit 45 transforms the photoacoustic image data to which the inverse filter is applied from a frequency domain signal to a time domain signal by Fourier inverse transform. An absorption distribution signal in the time domain is obtained by inverse Fourier transform.

By performing the processing described above, the optical differential term can be removed from the acoustic wave detection signal in which the optical differential term is convoluted, and the absorption distribution can be obtained from the acoustic wave detection signal. When such an absorption distribution is imaged, a photoacoustic image showing the absorption distribution image is obtained.

The correction means 46 corrects the data obtained by deconvolution of the optical pulse differential waveform, and removes the influence of the reception angle dependent characteristic of the ultrasonic transducer in the probe 11 from the data obtained by deconvoluting the optical pulse differential waveform. Further, the correction means 46 removes the influence of the incident light distribution of the light on the subject from the data obtained by deconvolution of the optical pulse differential waveform in addition to or instead of the reception angle dependent characteristics. Note that a photoacoustic image may be generated without performing such correction.

Claims

Based on this photoacoustic data, a pulsed light having a wavelength absorbed inside is emitted toward the subject, and the acoustic wave emitted from the subject is detected by the acoustic wave detecting means to obtain photoacoustic data. In the photoacoustic imaging method of imaging the subject and displaying it on the image display means,
A photoacoustic imaging method, wherein a pulse width of the pulsed light is adjusted according to a diagnostic characteristic required for a displayed image and / or a band of the acoustic wave detecting means.
2. The photoacoustic imaging method according to claim 1, wherein the diagnostic characteristic relates to a depth of a tissue desired to be imaged from a subject surface and image definition.
3. The photoacoustic imaging method according to claim 2, wherein the pulse width is set to be larger as the depth of the tissue to be imaged from the subject surface is larger.
The photoacoustic imaging method according to claim 2, wherein the pulse width is set to be smaller as the image definition is higher.
4. The photoacoustic imaging method according to claim 3, wherein the pulse width is set smaller as the image definition is higher.
The photoacoustic imaging method according to claim 1, wherein the pulse width is set to be smaller as the band is wider.
The photoacoustic imaging method according to claim 2, wherein the pulse width is set to be smaller as the band is wider.
The photoacoustic imaging method according to claim 3, wherein the pulse width is set smaller as the band is wider.
The photoacoustic imaging method according to claim 4, wherein the pulse width is set to be smaller as the band is wider.
Based on this photoacoustic data, a pulsed light having a wavelength absorbed inside is emitted toward the subject, and the acoustic wave emitted from the subject is detected by the acoustic wave detecting means to obtain photoacoustic data. In the photoacoustic imaging apparatus that images the subject and displays it on the image display means,
Condition input means for inputting information indicating diagnostic characteristics required for the displayed image and / or a band of the acoustic wave detection means;
A photoacoustic imager comprising: pulse width adjusting means for adjusting the pulse width of the pulsed light based on information input from the condition input means.
11. The photoacoustic imaging apparatus according to claim 10, wherein the condition input means inputs, as the diagnostic characteristics, a depth of a tissue desired to be imaged from a subject surface and an image definition. .
12. The photoacoustic image according to claim 11, wherein the pulse width adjusting means sets the pulse width to be larger as the depth of the tissue to be imaged from the subject surface is larger. Device.
12. The photoacoustic imaging apparatus according to claim 11, wherein the pulse width adjusting means sets the pulse width to be smaller as the image definition is higher.
13. The photoacoustic imaging apparatus according to claim 12, wherein the pulse width adjusting means sets the pulse width to be smaller as the image definition is higher. *
11. The photoacoustic imaging apparatus according to claim 10, wherein the pulse width adjusting unit sets the pulse width to be smaller as the band is wider.
12. The photoacoustic imaging apparatus according to claim 11, wherein the pulse width adjusting means sets the pulse width to be smaller as the band is wider.
13. The photoacoustic imaging apparatus according to claim 12, wherein the pulse width adjusting unit sets the pulse width to be smaller as the band is wider.
14. The photoacoustic imaging apparatus according to claim 13, wherein the pulse width adjusting unit sets the pulse width to be smaller as the band is wider.
When at least a part of the acoustic wave detecting means is detachable from the photoacoustic imaging apparatus main body, and the detachable part is attached to the photoacoustic imaging apparatus main body, The photoacoustic imaging apparatus according to claim 10, wherein information indicating the above is automatically input to the condition input unit.
Characterized in that it comprises optical differential waveform deconvolution means for generating, from the photoacoustic data, a signal obtained by deconvolution of a photodifferential waveform that is a differential waveform of the time waveform of the light intensity of the pulsed light received by the subject. The photoacoustic imager according to claim 10.