Optical resolution photoacoustic microscopy (OR-PAM), though possessing high lateral resolution, has been limited by its poor axial resolution. In this study, we adapt the delay-multiply-and-sum (DMAS) beamforming technique to improve axial resolution of OR-PAM without physically increasing the detection bandwidth. Experimental OR-PAM A-line signals from a thin absorbing layer were used to verify the efficacy of the proposed frequency domain DMAS method in axial resolution improvement. The improvement achieved with the proposed method was also further verified by imaging microvasculature of mouse ears in vivo.
Recently, radio-frequency (RF) delay-multiply-and-sum (RF-DMAS) algorithm has been proposed for photoacoustic (PA) imaging, featuring improved signal-to-noise ratio, contrast and lateral resolution. However, it requires oversampling to avoid aliasing and additional band-pass filtering (BPF) to keep the harmonic components for imaging. Here we propose baseband DMAS (BB-DMAS) algorithm for PA array imaging, offering similar results to the RF-DAMS ones but with simplified signal processing and additional flexibility. No oversampling and BPF is required. Experimental results show that the BB-DMAS algorithm provides similar image quality to the RF-DAMS one with lower complexity. The image quality can also be flexibly tuned accordingly.
Classic Doppler equation can only provide the axial velocity of blood flow. To acquire the complete flow vector,
estimation of the non-axial flow velocity is essential. For Doppler-bandwidth-based transverse estimation, however,
accuracy is limited because of the complex dependence of the Doppler bandwidth on the geometry and the location of
the sample volume in the vessel. Specifically, the Doppler bandwidth tends to be overestimated because it is
conventionally decided from the difference between maximum Doppler frequency and Doppler shift frequency. The
maximum Doppler frequency only depends on the peak flow velocity within the vessel and can be used as a stable
parameter in flow estimation. However, the Doppler shift frequency is susceptible to the position of the sample volume
and it decreases when the sample volume is not centered within the vessel. The distance between the center of the
sample volume and the central line of the vessel is referred to as the position offset of the sample volume. Based on the
stable nature of maximum Doppler frequency, a novel method utilizing the differential maximum Doppler frequencies
from two parallel beams with different beam widths is proposed to improve the accuracy of transverse estimation. In vitro
experiments were performed to validate the proposed method and results were compared with the conventional
method. In this study, a steady flow condition was considered and two 5-MHz pistons were used to generate the two
beams with different widths. For the conventional method, it is demonstrated that the Doppler bandwidth is severely
overestimated when the position offset is present. For the proposed method, however, the differential maximum Doppler
frequency is relatively stable even in the presence of the position offset as long as the sample volume is sufficient in
length. Hence, both accuracy and stability of the transverse estimation can be significantly improved by taking
advantage of the differential maximum Doppler frequency.
KEYWORDS: Tissues, Acoustics, Harmonic generation, Wave propagation, Signal to noise ratio, Signal detection, Transducers, Ultrasonography, Nonlinear optics, Signal generators
Generation of tissue harmonic signals during acoustic propagation is based on the combined effect of two different
spectral interactions of the transmit signal. One produces harmonic whose frequency is the sum of transmit frequencies.
The other results in harmonic at difference frequency of the transmit signals. Both the frequency-sum component and
the frequency-difference component are sensitive to the phase of their constitutive spectral signals. When the two
components are in-phase, enhancement of the native harmonic signal is feasible. Otherwise, they may cancel out each
other and result in weak harmonic amplitude. For the frequency-sum component, its phase is solely related to the
fundamental signal in the transmit waveform. On the other hand, the phase of the frequency-difference component is
determined by the phase difference between the third harmonic signal and the fundamental signal. Results indicate that
the relative phasing between the frequency-sum component and the frequency-difference component significantly
changes the amplitude of the second harmonic signal. By simultaneously transmitting both fundamental signal and third
harmonic signal with proper phases such that the frequency-difference component is in-phase with the frequency-sum
component, the amplitude of second harmonic signal can be increased while the lateral harmonic beam pattern remains
unchanged as compared to conventional situations. The second harmonic signal could be also reduced significantly
when the two components are out of phase. Hence, third harmonic transmit phasing has potential for improving signal-to-
noise ratio in tissue harmonic imaging or for enhancing image contrast in contrast agent imaging by suppression of
tissue harmonics.
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