Photoacoustic needle: minimally invasive guidance to biopsy

Abstract. We introduce a needle probe based on photoacoustics (PA) to extend the scope of optical needle methods in guiding biopsies. Pulsed light is coupled to an optical fiber in a needle to be inserted in tissue, and PA signals are detected using an ultrasound imager used for needle guidance. This PA needle samples large volumes and possesses an imaging component so that sites forward and off-axis of the fiber are surveyed. This allows navigation of those regions for optical characterization and direct biopsy in a subsequent step. The concept is explored on simple phantoms and biological specimens.

Biopsy is the gold standard for diagnosis of cancer in organs like the breast. 1 Samples are extracted through a needle under ultrasound (US) or stereotactic x-ray imaging. The size of samples is a few cubic millimeters in core needle biopsy (CNB). Samples are histologically examined for the presence of cancer cells and, if positive, tumor type and grade are ascertained. Further, vascular channel invasion and molecular markers are ascertained. 2 However, imaging methods have drawbacks: US and x-ray imaging suffer from limited sensitivity and specificity, and needle visualization is poor in US. 3 Coupled with the spatial heterogeneity of cancers, the sampled tissue may not be representative of the pathology: cancers are missed in 4.3% to 17.9%, and repeat biopsies are needed in 4% to 32% of cases. 4 Optical fiber-based probes that insert into biopsy needles have been developed 5 and can provide spectroscopic assessment of tissue to guide the biopsy in a further step. These techniques rely on wavelength-dependent differences in optical properties between cancerous and normal tissues. 5 Optical properties are estimated by fitting models of photon propagation in tissue using a priori knowledge of the spectral behavior of expected chromophores. The estimated absorption and reduced scattering coefficients are indicative of physiological and structural properties averaged over volumes not exceeding 5 to 10 mm 3 .
We aim to extend the scope of the optical method by sampling larger volumes of tissue for optical properties, while attaching spatial information to this contrast. We add an imaging component to the method so that the sites forward and off-axis of the fiber tip are surveyed by using photoacoustics (PA). The method has the advantage of high optical absorption contrast possible in optical imaging, and high spatial resolution associated with US. Light absorption, followed by fast nonradiative de-excitation and temperature rise, leads to localized thermoelastic expansion. The resulting pressure waves propagate to the tissue surface and are registered using US transducers. 6,7 In our concept, the PA needle, we use pulsed light in a fiberbased needle probe to excite PA waves in the vicinity of a lesion. Light is delivered inside the tissue in contrast with noninvasive PA imaging for biopsy guidance. 3 The excitation is close to the region of interest, reducing light losses, while adapting to the setting of biopsy. The US imager used for needle guidance performs PA detection. To demonstrate feasibility, we present first results in phantoms and biological specimens. A first estimation of optical properties is performed, while demonstrating the imaging capabilities.
The system ( Fig. 1) consists of a US imager (Picus, Esaote Europe BV, Maastricht) with a linear array transducer L10-5 (128 elements, 7.5 MHz, 75% bandwidth). 7 A multimode optical fiber (NA 0.22, diameter 600 μm) delivers 10 ns laser light at 1064 nm (Diny pQ, IB laser, Berlin) with 1.4 mJ∕pulse at 250 Hz. The PA frame rate is 2 Hz and images are reconstructed online with a phased-array algorithm. The fiber is held in a metal housing (biopsy needle 14 G × 13 cm, Bard Ltd, UK) and fixed with Stycast discs (Fig. 1). Finally it slide-fits into a 14 G cutting cannula. A 2-mm cube of poly(vinyl alcohol) (PVA) ( Table 1) is used as insert, held on a nylon thread and submerged in a liquid bath at 5 cm from the transducer. The bath contains solutions of Intralipid 20% (Fresenius Kabi, Germany) and Intralipid/ Ecoline Black (nr. 700, Royal Talens, The Netherlands), with optical properties shown in Table 1. The PA needle is moved at a 45-deg orientation towards the insert. PA frames are acquired at several distances (18 averages, 10 to 20 frames, 0.5 mm step) between the fiber tip and insert.
In Fig. 2, results for experiment A are shown. In each frame [ Fig. 2(a)] we see high intensity from the fiber tip (PA fib ) and from the insert (PA ins ). In Fig. 2(b), all frames are summed up: we observe the trace of PA fib along the 45-deg path. The insert is visualized, though the front face dominates due to the higher fluence at that point and to the limited bandwidth of the transducer (Fig. 2, insets). In Fig. 2(b) (inset) front and back surfaces of the insert are seen 2 mm apart. For each frame rectangular ROIs including insert and fiber signals are selected. The fiber to insert distance (r) is defined as the distance between the coordinates of maximum signal (PA max ) in the two ROIs. Average values of PA ins and PA fib are calculated in a −6 dB threshold with respect to PA max , and plotted against r. In Fig. 2(c), curves for experiment A are reported. With decreasing r, PA ins increases, while PA fib is constant, except for a steep increase close to the insert.
Under diffusion approximation, with μ a;m and μ 0 s;m medium optical properties, and μ a;ins insert absorption coefficient, for every r i along the needle axis, the insert absorbed energy density E a;ins can be written as where Φ 0 is the fluence at the fiber interface and μ eff;m ¼ ffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffiffi 3μ a;m ðμ a;m þ μ 0 s;m Þ p is the medium effective attenuation coefficient. We assume that PA fib is constant for every position of the needle along its trajectory. This first approximation for the simple phantoms used will lose validity in the case of optical heterogeneity. In future work, a model-based approach can avoid this assumption. By fitting Eq. (1) to the experimental data, we obtain μ eff;m . 8 For experiments A (nine measurements) we report mean and standard deviation of estimated μ eff;m , for experiments B and C (one measurement each) we report the estimated μ eff;m with 95% confidence bounds (Table 1). Good agreement between actual and estimated μ eff;m is found (Table 1), with error less than 20%. It is possible to quantify μ eff;m of a homogeneous medium in a large probing volume     Table 1): (a) single frame, (b) sum of all frames. The insert is enlarged in the insets in (a) and (b). (c) PA ins (measurements and fit) and PA fib (measurements) against fiber tip to insert distance.
(at least 5 mm on axis) and obtain location and size of the insert.
To further demonstrate the imaging capability we used chicken breast as a background material, and a 1.5 × 1.5× 0.5 cm 3 blood rich heart of a fish (Sparus aurata) as insert [ Fig. 3(a)]. Figure 3(a) shows the schematic of the experiment. Figure 3(b) and 3(c) shows two frames for two positions of the PA needle. Apart from the bright PA fib , PA intensities from the chicken breast are visible in Fig. 3(b). In Fig. 3(c), we see a heterogeneous distribution of high intensity spots where the heart is located. No remarkable US reflections can be recognized. Summing up all PA frames [ Fig. 3(d)] we see the path of the needle, and an extended high intensity PA region at the heart location. US confirms the position of the needle and heart [ Fig. 3(e)]: the heart is moderately more echogenic than the chicken breast (1.14 contrast), and the needle is barely visible (1.12 contrast). The heart is then ground into small structures to represent the heterogeneities of a tumor. 9 The PA image is shown in Fig. 3(f). PA contrast is better than US contrast in all cases: 34% higher for intact heart; 48% higher for ground heart (US not shown), and 17% higher for the needle.
In summary, we introduced the PA needle concept and have shown that it can supplement optical property estimation, in a minimally invasive setting, with imaging capabilities. The needle is identified in PA with superior visibility to US imaging. We derived μ eff;m when forward lying absorbing targets are probed. A ground fish heart representing a heterogeneous cancer is imaged in a challenging biological medium: at this stage, we cannot exclude that US reflections from the tip affect the PA images at the position of the heart. We intend to work on a model-based approach to invert a forward model by iteratively fitting it to the PA measurements. With instrumental improvements 10 and multiple wavelengths 11 it might make possible quantitation of μ a;ins and μ a;m , providing powerful discrimination capabilities for guiding biopsy in breast care.   Journal of Biomedical Optics 070502-3 July 2013 • Vol. 18 (7)