Intelligent medical image landmark detection

[0001] This application claims the benefit of the filing date under 35 U.S.C. §119(e) of U.S. Provisional Application No. 62/219,432, filed Sep. 16, 2015, and U.S. Provisional Application No. 62/254,601, filed Nov. 12, 2015, which are hereby incorporated by reference in its entirety.

[0002] The disclosure is generally directed to medical image landmark detection, and more particularly, to machine learning for navigation of image parsing with deep reinforcement learning.

[0003] Knowledge-driven computational models are at the core of machine learning. As known in the conventional art, knowledge-driven computational models provide automation of image processing emulating intelligence and learning from a human perspective. In general, intelligent behavior is viewed as the ability of a computer, an individual, or artificial entity to explore, learn, and understand tasks, as opposed to mechanically following pre-defined steps.

[0004] Automation of image processing transcends the speed and capabilities of image analysis performed by a person. Machine learning techniques based on prediction, classification, and recognition using data-driven learning algorithms expand the capabilities of computers and artificial entities beyond the repeated, mechanical execution of a set of pre-defined steps. Known machine learning methods follow pre-defined steps such as sequentially and exhaustively scanning for feature extraction within medical images from patients, even after a classifier has been trained to recognize features.

[0005] Conventional methods of machine learning-based medical image parsing focus on generating rigid classifiers trained using observation anchored in a parametric space to learn appearance models. A classifier learns its appearance models through training, that applies rigid sets of pre-defined steps. In training, the classifier analyzes given data examples based on handcrafted features. That is, method-related meta-parameters (e.g., regularization weights, ranges, scales) are hand-picked or tuned according to application-specific criteria. Parameter optimization is limited due to the general use of handcrafted features. Weak generalization is due to overfitting. An operator, engineer, or medical professional is required to understand the variability of the desired medical imaging analysis and identify a suitable model or set of meta-parameters to reach optimal performances. The computer then blindly executes its task to automate the medical imaging analysis.

[0006] Machine learning techniques for quickly identifying anatomy in medical images include Marginal Space Learning (MSL), deep learning such as Marginal Space Deep Learning (MSDL), Marginal Space Deep Regression (MSDR) and Approximated Marginal Space Deep Learning (AMSD). These machine learning techniques each employ efficient machine learning frameworks to analyze large medical image databases to determine relevant image features. Classifiers are trained to identify the learned relevant image features generated from the input space parameters. Accordingly, in order to create efficient computerized medical image analysis, classifiers and machine learning frameworks are individually customized to a specific medical image analysis task. Separate solutions must also be hand crafted to perform a medical image analysis task specific to the imaging modality of the acquired image data.

[0007] Improvements may be made in machine learning techniques, such as techniques for automated landmark detection in medical imaging. Systems, methods and non-transitory computer readable medium are provided for generating, training, and deploying an artificial agent for intelligent landmark identification in images, including medical images of a patient. The disclosed system constructs an agent that both learns how to identify the location of an anatomical landmark in a set of image data and how to generate its own model of the task to perform by automatically determining an optimal policy for conducting image evaluation and identify one or several anatomical landmarks.

[0008] A method is provided intelligent image parsing. The method specifies a state space of the artificial agent for discrete portions of a training image. A set of actions is determined, each action specifying a possible change in a parametric space with respect the test image. The reward value can indicate, for instance, a distance metric between the current state space and a landmark target of the medical image. An action-value function approximator is defined that specifies the behavior of the artificial agent. The optimal action-value function is learned to maximize a cumulative future reward value based on the reward system, the set of actions, and the state space, wherein the behavior of the artificial agent can be defined as the ability to select a next action to position the state space on the landmark target of the medical image such that the long term reward is favored.

[0009] A system for artificial agent training for intelligent landmark identification in medical images is provided. The system includes at least one processor and at least one memory including computer program code for one or more programs. The memory and the computer program code are configured to, with the processor, cause the system to evaluate a state space of discrete portions of each training image of a set of training images, wherein training images of the set of training images includes a landmark target, wherein the landmark target is marked on each training image. The system is further caused to change a position of the state space with respect to each training image via application of actions of a pre-defined set of actions and determine a reward value of each position change of the state space based on a reward system. The reward value is indicative of a proximity of a current state space to a pre-defined landmark target of each training image. The system is further caused to optimize behavior of the artificial agent based on maximizing a cumulative future reward value based on the reward system, the set of actions, the state space, and the set of training images. The behavior of the artificial agent is defined as intelligent selection of next actions to achieve a position of the state space on the landmark target a medical image of a patient.

[0010] A non-transitory computer readable medium is provided including instructions that may be executed by a microprocessor. When executed, the instructions are operable to receive a medical image of a patient; and apply optimized behavior of an artificial agent. The application of optimized behavior includes selection of actions from a pre-defined set of actions to change the position of the state space relative to the medical image, evaluation of discrete portions of the medical image defined by a position of the state space of the artificial agent relative to the medical image, and determination of a location of the target landmark when present in the medical image evaluation. Through the reward system, the agent can also know if a landmark is not present in the image when no good reward can be obtained.

[0011] The present invention is defined by the following claims, and nothing in this section should be taken as a limitation on those claims. Further aspects and advantages of the invention are discussed below in conjunction with the preferred embodiments and may be later claimed independently or in combination.

[0029] The conventional art fails to provide systems and methods that can understand the given problem by extracting knowledge and applying reasoning to generate a solution. The structure, training, and application of the conventional classifier does not permit the incorporation or discovery of intrinsic knowledge associated with the task execution, itself. Conventional solutions based on the handcrafted model are completely decoupled from this higher level of understanding, capable only of blindly executing the solution. The manual customization of the parameterized search sequence, rigidity in the order of applying classifiers, and/or manual pre-determination of specific dependent parameters distributions in the conventional machine learning techniques are difficult to scale to a large number of objects. The sequential and exhaustive scanning is repeated uniformly for each image scan based on a pre-defined set of scanning instructions, whereas the disclosed embodiments do not require such input. The artificial agents of the disclosed embodiments may be said to develop a set of scanning instructions, essentially “learning” to scan.

[0030] Fast and robust medical detection of anatomical structures, anatomical landmarks, and/or anatomical anomalies is beneficial to medical image analysis. Conventional machine learning-based medical image landmark detection is limited to learning an appearance model and exhaustively scanning the space of parameters to find the optimum point, yielding suboptimal and unconstrained solutions. Feature computation and estimation of any other meta-parameters related to the appearance model or the search strategy of the conventional art are performed based on local criteria or predefined heuristics, leading to the rigid application of a specific search strategy applicable to a highly specialized task.

[0031] A goal of some of the present embodiments is to address limitations of the conventional art in medical image analysis by simultaneously automating the modeling of both object appearance and the parameter search strategy as a unified behavioral task via an artificial agent. The disclosed embodiments achieve both the advantages of optimizing the execution of behavior learning through reinforcement learning with effective hierarchical feature extraction through deep learning. That is, given only a sequence of annotated images, the agent automatically learns strategies to localize image landmarks at a high accuracy. A further goal of the disclosed embodiments is to create a robust solution facilitating evaluation of images obtained by a variety of different medical imaging devices while achieving average detection errors of less than one to two pixels. A further goal is to automatically determine when an anatomical landmark is not contained within a medical image obtained from a patient. The disclosed embodiments advantageously create machine-driven image understanding in the context of medical image parsing. Physicians may benefit from the accurate, precise, specific, and/or sensitive detection in a medical image, aiding diagnosis using medical imaging technology.

[0032] The disclosed embodiments can be directly applied to automatic parsing of a medical image regardless of its source (e.g., equally robust for computed tomography, magnetic resonance, ultrasound, x-ray, molecular, or other modalities). As in FIG. 1, an artificial agent is generated and trained to self-develop an optimized method for efficiently identifying an anatomical landmark. Large numbers of search parameters evolve over the course of training the agent on a set of identified landmark targets. The agent begins a training set freely and randomly navigating through the image via the state space. Gradually, the agent learns a policy during training to optimize the expected reward value r_t of its actions. Expected rewards are determined by the reward value of the possible actions, a, available to the agent at time, t with the goal of identifying the target landmark (via maximizing expected reward value). Actions, a, define the positional movement that occurs during state space transitions with respect to the state space's proximity to the target landmark. Sequential actions are determined and stored by the agent, and, ∇_w, ∇_b, and simultaneously with landmark detection, eliminating the need to hand-craft optimization criteria, image features, or exhaustive image search. The artificial agent can be applied to object detection, segmentation, tracking, and/or image registration, beneficially advancing systems based on medical imaging.

[0033] In the context of medical image parsing, disclosed embodiments provide machine driven image understanding by formulating the landmark detection problem as a generic learning task for an artificial agent. Representation learning techniques through deep learning and solutions for generic behavior learning through reinforcement learning provide a model encapsulating a cognitive-like learning of a process leading to the discovery of strategies for finding the locations of arbitrary landmarks, using only the raw image input information and the landmark annotations. Opposed to standard machine learning methods, optimization of the landmark appearance model is integrated with the location parameters in a joint behavioral optimization. The flow diagram of FIG. 2, further expands on FIG. 1. The artificial agent functions in primarily two phases, training and testing. In the training phase, the agent learns to optimize its selection of its actions based on pre-defined landmark targets marked on input images. In the testing phase, medical images of patients are input in order for the agent to locate the pre-defined landmark targets in the manner learned by the agent during the training phase.

[0034] The disclosed embodiments advance the conventional art in machine-driven image understanding in the context of medical image parsing by formulating a landmark detection problem as a generic learning task for an artificial agent. Representation learning techniques through deep learning and solutions for generic behavior learning through reinforcement learning are provided. A goal is to encapsulate a cognitive-like learning process leading to the discovery of strategies for finding the locations of arbitrary landmarks, using only the raw input image information and the landmark annotations. Unlike conventional machine learning methods, the disclosed embodiments integrate the optimization of the landmark appearance model and the location parameters in a joint behavioral optimization framework. Reinforcement learning and deep learning may surpass human performance. A goal is to model the landmark detection problem in the context of medical image parsing as a behavioral task for an artificial agent.

[0035] Constructing artificial agents that are capable of emulating and surpassing human performance for a given task, conventionally require the use of an automatic, generic learning model observed not only in exploratory, unsupervised human cognition but also in basic reward-based animal learning methods. The artificial agent is equipped with at least two fundamental capabilities found at the core of the human and animal intelligence. At a perceptual level is the automatic capturing and disentangling of high-dimensional signal data which describes the complete situation in which the agent can find itself, while on cognitive level is the ability to reach decisions and act upon the entire observed information flow.

[0036] Accurate landmark detection is a fundamental prerequisite in medical image analysis. In one application, the disclosed method may be employed in both the contexts of cardiac magnetic resonance imaging (MRI) and cardiac ultrasound imaging, which are frequently used for structural and functional analysis of the heart. Other imaging modalities and/or anatomy may be used.

[0037] Short-axis cardiac MR images, such as FIG. 3A, provide a cross-sectional view of the left and right ventricles (LV and RV). In these types of images, particular landmarks may define important anatomical features of the heart such as the LV-center (also called left-ventricular basis central access point), the anterior RV-insertion, the posterior RV-insertion, and RV-extreme points. Accurately identifying any one or more of these or other landmarks represents a step in the context of part modeling. For example, the right ventricular insertion points and extreme point can be used to initialize the 3-D segmentation model and impose constraints on the shape of the right ventricle.

[0038] In one non-limiting example, an initial data set may contain approximately 1000 short axis view MR images acquired from several hundred different patients acquired from different vendors and formed into hundreds of training images. The training images may be preprocessed, such as resampling images to uniform, isotropic resolution (e.g. 2 mm) and normalizing the data. A cross validation set may be used to quantify the performance during training. The disclosed method achieves the goal of increased accuracy on the test set presenting more accuracy than is currently available in conventional methods.

[0039] In order to learn optimal action policy in a sequence of learning episodes, the agent is given random training images with corresponding random start-states. The agent then follows an E-greedy search strategy in the selected image, generating, at the end of the episode a trajectory which is added to its experience memory. During the exploration, periodic updates are applied to the parameters of the neural network, leading to a more accurate approximation of the optimal Q* function, given the current experience. This process is repeated in an iterative manner until the detection accuracy on the validation set is minimal.

[0040] Experiments on the network architecture and training parameters are the same regardless of the dimensionality of the medical image and the medical imaging modalities that will be subjected to a trained agent. In some embodiments, the agent may be trained using root mean square (RMS)-prop mini-batch approach, which may provide the benefit of improved performance over standard stochastic gradient descent. In one example, the learning rate is set to η=0.00025, justified by the sparse sampling applied in experience replay, while the discount factor is fixed to 0.9. Other parameters important to training are the replay memory size (100000 view-patches) and ε=0.8 decaying linearly to 0.05.

[0041] FIG. 3A-3B illustrate various points examples significant anatomical landmarks in two different imaging modalities, MR and ultrasound, respectively. Regarding cardiac MR image FIG. 3A, landmark 1 represents the left-ventricular base central axis point (LV-center). Landmark 2 represents the right-ventricular point. Landmarks 3 and 4 represent the anterior and posterior RV-insertion points, respectively. FIG. 3B illustrates Landmark 1 of the ultrasound image as the mitral septal annulus, and landmark 2 as the mitral lateral annulus point. FIGS. 4A-4C illustrate performance evolution during artificial agent training in these two modalities. The high standard deviation of the detection accuracy is correlated with divergent trajectories, given the random initialization of the policy. However, as the policy improves, the detection accuracy increases, reaching the maximum point when all trajectories converge to the correct landmark position. Table 1 illustrates the detection error in short-axis MR images from a test set. The detection error is quantified as the distance to the ground-truth, measured in mm.

[0042]

TABLE 1
Detection Error [mm]
	Landmark Type	Mean	Median	STD
	LV-center	1.85	1.76	2.23
	RV-extreme	4.94	4.24	3.65
	RV-insertion ant.	3.72	3.05	2.33
	RV-insertion post.	2.17	1.78	1.55

[0043] The plots of FIG. 4B illustrate, the average expected reward of the LV-center landmark agent and the RV-insertion posterior landmark agent, respectively, as computed for random states that are kept fixed across the training stages. The plot of FIG. 4C shows the progression of the mean squared error in the Bellman equation. The quality of the learned policy may be quantified to determine the number of training rounds based on the mean detection error on the cross validation set. Table 2 illustrates the detection error in an exemplary analysis of cardiac ultrasound images from the test set. The detection error is quantified as the distance to the ground-truth, measure in pixels.

[0044]

TABLE 2
Detection Error [pixels]
	Landmark Type	Mean	Median	STD
	Mitral septal annulus	1.27	1.17	0.83
	Mitral lateral annulus	1.62	1.28	1.40

[0045] During the evaluation, the agent starts in a random or predefined state (e.g. expected landmark location based on the ground truth) and follows the computed policy, iterating through the state space until an oscillation occurs (an infinite loop between two adjacent states). The end state is considered a high confidence solution for the position of the target landmark, if the expected reward max_a Q*(s_target, a)<1 (closer than one pixel). If this is not the case, the search has failed. One benefit of the disclosed embodiments provides an effective confidence measure for the performance of the agent. FIGS. 8A-8D depict visualizations of the optimal action-value function Q*, with each state space encoding the highest expected reward, considering all actions that may be taken in that state.

[0046] In addition to detection of divergent trajectories, this confidence measure can also indicate that the landmark is not contained within the image. In one non-limiting example, trained artificial agents are applied to 100 long axis cardiac MR images from different patients. The performance evaluation determines that oscillation occurs at points where the expected future reward is significantly high as illustrated in plots of FIG. 4A. Oscillation with a significantly high expected future reward indicates the low confidence of the result. The same holds true also for divergent trajectories in images with the landmark.

[0047] The accuracy of convergence to a solution is largely independent of the location of the beginning position of the start state in relation to the medical image. In randomly selected test images evaluated for convergence, more than 90% of the possible starting points converged to the correct solution as shown in image 520 of FIG. 5. Image 520 illustrates the boundary of the state space (limited such that image margins cannot be crossed) in dashed lines, individual starting coordinate location locations appearing as shaded regions indicating that the vast majority of possible starting points result in successful identification of the landmark target. In other words, only three random attempts can indicate a probability of diverging to a degree of less than 0.1%. FIG. 5, image 500, illustrates example trajectories converging to the landmark position. Image 510 illustrates divergence of the trajectories into a sub-optimal region. Images 500 and 510 illustrate the starting point on the right, target landmark on the left with trajectories illustrated as a white path ending at the detection result.

[0048] Identical learning parameters and network structure may be used with different imaging modalities. For example, the disclosed method may also be used in cardiac ultrasound imaging. Ultrasound images of a four chamber view may have the target identification of two mitral valve annulus points: the mitral septal annulus and mitral lateral annulus points (see FIG. 3B). Here, the data set may include approximately 1000 images from several hundred patients that are used to construct randomly selected data subsets for agent training, cross-validation of the trained agent, and quantification of trained agent performance. The data sets respectively include approximately 1000 training images, 100 cross-validation, and 100 test images. Preprocessing may be applied such as normalization and resampling steps as in the cardiac MR example data set. Table 2 shows the detection error. FIG. 6 images 600-660 illustrate example trajectories as a white path in tests of an MR image for the four landmarks identified in FIG. 3A. Images 600 and 610 illustrate trajectories for the LV-center landmark with starting locations at the bottom of the images and convergence with the target landmark at the top of the images. An RV-extreme landmark is the target of image 620, with starting position of the agent at the bottom of the image and target at the top. Image 630 and 640 illustrate the posterior RV-insertion point as the target landmark. Images 650 and 660 illustrate the anterior RV insertion point. The starting position of image 630 is located at the top of the image and at the bottom of images 640, 650, and 660. FIG. 7 illustrates example trajectories of the ultrasound landmarks illustrated in FIG. 3B. The mitral septal annulus is identified as the landmark target in ultrasound image 700 and the mitral lateral annulus points are the targets of images 710 and 720. Each starting position is indicated towards the bottom of the image, with the trajectories visualized as white paths illustrating successful convergence at the top most point, the landmark target. The mean accuracy of less than 1.7 pixels with no outliers indicates the robustness of the approach on different modalities.

[0049] Deep Representation Learning

[0050] Deep learning (DL) techniques are used to generate intelligence of the artificial agent of the disclosed embodiments, allowing the artificial agent to learn (e.g., optimize behavior). DL techniques are conventionally applied to various problems ranging from image classification, object detection and segmentation, and speech rate recognition to transfer learning. Deep learning is the automatic learning of hierarchical data representations describing the underlying phenomenon. That is, deep learning proposes an automated feature design by extracting and disentangling data-describing attributes directly from the raw input in contrast to feature handcrafting. Hierarchical structures encoded by neural networks are used to model this learning approach.

[0051] The convolutional neural network (CNN) mimics non-cyclic, feed-forward type of information processing observable in the early visual cortex. This learning emulates, automates, and improves the principles of animal and human receptive fields. Deep fully connected neural networks include multiple layers. Each layer learns a more abstract and insightful data representation using the output from the previous layer. Hierarchical layers of translation-invariant convolutional filter kernels are constructed based on local spatial correlations observable in images. As illustrated in FIG. 2, Convolutional Neural Network Q* includes multiple layers l₁-l_n. Convolutional layer l₁ may include 32 6×6 kernels feeding into 2×2 pooling-layer, l₂. The pooling layer then feeds into convolutional layer l₃ including 46, 4×4 kernels feeding into 2×2 pooling-layer l₄. Further layers include l_4-n, which may be fully-connected layers 512×128×64. Q* values are output for each of the possible actions of left, right, up, and down.

[0052] The application of the filter kernel to the data generates a representation of the filtered data at each layer, called a representation map. The representation map generated by the l-th convolutional filter kernel in the layer k by {right arrow over (ω)}^(k,l), is represented by Equation 1:
o_i,j=σ(({right arrow over (ω)}^(k,l)*{right arrow over (x)})_i,j+b^(k,l))  Eq. 1
where x is the representation map from the previous layer used as input for the l-th convolutional filter kernel, (i,j) defines the evaluation location of the filter and b^(k,l) is the bias of the considered output neuron. The function σ represents the activation function used to synthesize the input information. Possible alternatives to the above activation function may be selected based on the given learning problems. Examples of learning problems include classification, multi-class classification or regression, and example alternative functions include the sigmoid function, hyperbolic tangent, or rectified linear units (ReLU).

[0053] Given a set of scalar or matrix data of independent observations “•”, such as input patches {right arrow over (X)}, and corresponding value assignments {right arrow over (y)}, the network response function may be defined as R(•; {right arrow over (ψ)}, {right arrow over (b)}). Thus, a Maximum Likelihood Estimation to estimate the optimal parameters for the CNN results as Equation 2:

[0054] $\begin{array}{cc}\stackrel{->}{\omega },\stackrel{->}{b}=\arg \begin{array}{c}\max L\\ \stackrel{->}{\omega },\stackrel{->}{b}\end{array}\left(\stackrel{->}{\omega },\stackrel{->}{b}\right)=\arg \begin{array}{c}\min \\ \stackrel{->}{\omega },\stackrel{->}{b}\end{array}{R\left(\stackrel{->}{X};\stackrel{->}{\omega },\stackrel{->}{b}\right)-\stackrel{->}{y}}_2^2& \mathrm{Eq}.2\end{array}$

[0055] The optimization may be solved with the Stochastic Gradient Descent (SGD) method or rms-prop in a mini-batch approach. Using a random set of samples X from the training input, a feed-forward propagation is performed to compute the network response R({right arrow over (X)}; {right arrow over (ω)}, {right arrow over (b)}). Denoting {right arrow over (ω)}(t) and {right arrow over (b)}(t), the network parameters in the t-th optimization step are updated according to Equation 3:
{right arrow over (ω)}(t+1)={right arrow over (ω)}(t)−η∇_wE({tilde over (X)};{right arrow over (ω)}(t),{right arrow over (b)}(t))
{right arrow over (b)}(t+1)={right arrow over (b)}(t)−η∇_bE({tilde over (X)};{right arrow over (ω)}(t),{right arrow over (b)}(t)),  Eq. 3

[0056] where ∇ is the gradient of the cost function with respect to the network parameters, η the magnitude of the update. That is, the learning rate, and E({tilde over (X)};{right arrow over (ω)}(t),{right arrow over (b)}(t))=∥R({right arrow over (X)};{right arrow over (ω)},{right arrow over (b)})−{right arrow over (y)}∥₂² represents the error function. Backpropagation may be used to compute and apply the gradient to the network parameters.

[0057] Reinforcement Learning

[0058] The disclosed embodiments use DL in conjunction with Reinforcement learning (RL). RL is a technique facilitating learning as an end-to-end cognitive process for an artificial agent, instead of a predefined methodology. One RL setting is composed by an artificial agent that can interact with an uncertain environment (e.g., medical image of a patient without landmark target identified) with the target of reaching pre-determined goals (e.g., identifying the landmark target in the image). The agent can observe the state of the environment and choose to act on the state, similar to a trial-and-error search, maximizing the future reward signal received as a response from the environment. The main system diagram of FIG. 1 illustrates an artificial agent interacting with portions of an image defined by a mobile state space s_t. Optimal action-value function approximator Q* estimates the agent's response to image data as measured by state space s_t. in the context of a reward function r_t. This reward-based decision process is modeled in RL theory as a Markov Decision Process (MDP) defined by a tuple M:=S, A, T, R, γ, where S is a finite set of states and s_tεS is the state of the agent at time t. A is a finite set of actions allowing the agent to interact with the environment, and a_tεA is the action the agent performs at time t. T:S×A×S→[0; 1] is a stochastic transition function, where T_s,a^s′ is the probability of arriving in state s′ after the agent performed action a in state s. R:S×A×S→ is a scalar reward function, where R_s,a^s′ is the expected reward after a state transition. γ is the discount factor controlling the importance of future versus immediate rewards.

[0059] The future discounted reward of an agent at time {circumflex over (t)} can be written as R_{{circumflex over (t)}}=

[0060] $\sum _{t=\hat{t}}^T{\gamma }^{t-\hat{t}}{r}_t,$
with T marking the end of a learning episode and r_t defining the immediate reward the agent receives at time t. In model-free reinforcement learning, the target may be to find the optimal so called action-value function, denoting the maximum expected future discounted reward when starting in state s and performing action a as in Equation 4:
Q*(s,a)=max_π[R_t|s_t=s,a_t=a,π]  Eq. 4
where π is an action policy. That is, the action policy is a probability distribution over possible actions in each given state. Once the optimal action-value function is estimated, an optimal action policy determining the behavior of the agent can be directly computed in each state as Equation 5:
∀_sεS:π*(s)=argmax_aεAQ*(s,a)  Eq. 5

[0061] The optimal action-value function approximator Q* is the Bellman optimality equation, representing a recursive formulation of Equation 4, defined as Equation 6:

[0062] $\begin{array}{cc}{Q}^{*}\left(s,a\right)=\sum _{s^{\prime }}{T}_{s,a}^{s^{\prime }}\left(R_{s,a}^{s^{\prime }}+{\mathrm{\gamma max}}_{a^{\prime }}{Q}^{*}\left(s^{\prime },a^{\prime }\right)\right)& \mathrm{Eq}.6\end{array}$
where s′ defines a possible state visited after s, a′ the corresponding action and r=R_s,a^s′ represents a compact notation for the current, immediate reward. Viewed as an operator T, the Bellman equation defines a contraction mapping. Applying Q_i+1=τ(Q_i), ∀(s, a), the function Q_i converges to Q* at infinity. This standard, model-based policy iteration approach is, however, not feasible in practice. An alternative is the use of model-free temporal difference methods, typically Q-Learning, which exploits correlation of consecutive states, is more applicable in practice. Using parametric functions to approximate the Q-function furthers a goal of higher computational efficiency. Considering the expected non-linear structure of the action-value function, neural networks represent a sufficiently powerful approximation solution.
System Operation

[0063] The landmark detection problem is addressed by developing an artificial agent characterized as a reinforcement learning problem. The artificial agent learns (e.g., develops the landmark detection solution) during training with a set of N training images I₁, I₂, . . . , I_N. Each contains M annotated landmarks. Focusing on one particular landmark indexed in each training example, the method trains an artificial, intelligent agent that can automatically discover strategies for finding the chosen landmark not only in the provided data, but also in unseen examples. The problem is defined as a Markov Decision Process M:=(S, A, T, R, γ). The state and action spaces are specified and the reward system is defined. Transition probabilities T are unknown in the disclosed, model-free embodiment.

[0064] The depicted methods of FIGS. 9-12 may be executed by imaging system 48 and/or processor 50. Program data, input, intermediate or output data may be partially or completely stored on Memory 52, FIG. 9 illustrates a flow diagram in accordance with one disclosed embodiment for generating an artificial agent for intelligent image parsing. The acts are performed in the order shown or other orders. Additional, different, or fewer acts may be provided. For example, the method is performed without act B911.

[0065] The method disclosed in FIG. 9 depicts a flow chart for intelligent image parsing. In act B901, a state space of an artificial agent is specified for discrete portions of a training image. For example, the state space has a length and width expressed as a number of pixels, with a focal point defined as the center coordinate of the set of pixels. In act B903, a set of actions is determined, each action specifying a possible change in a parametric space with respect to the test image. The set of action may include changing a position, an orientation, a scale, or a shape of the current state. The set of actions may be defined as any possible incremental changes in position of the state space that can be made by the agent. For example, a set of actions may be defined as movements of the state space position one pixel in each direction that the agent may select from the set of upwards, downwards, left, or right. The set of actions may additionally include an action in which state space remains in the same position without movement. The set of actions may be selected to provide optimal sets of measurements during agent training.

[0066] In act B905, a reward system is established based on applying each action of the set of actions and based on at least one target state. A reward value is determined by the value of the agent's selection of an action. Success is determined by the proximity of the current state space to the target state (e.g., landmark target). The target state may be an anatomical landmark with the state space defined by the position parameters of the anatomical landmark. The associated reward value may be indicative of a proximity of a current state space to the at least one target state. For example, the reward value may be ±1 for each action. The reward value of a single move can be any fractional proportion expressing the reward of the action. That is, an agent selecting an upward action has a maximum reward value when the focal point of the state space is vertically below the landmark target. When the focal point of the state space is neither exactly above, below, left, or right of the focal point of the state space, a maximum reward value cannot be attained by any upward or downward action because the set of actions is limited to upward, downward, left, and right movements at increments of one pixel.

[0067] In act B907, an optimal action-value function approximator is learned by the artificial agent. The optimal action-value specifies the behavior of the artificial agent in order to maximize a cumulative future reward value based on the reward system. The behavior of the artificial agent is a sequence of actions moving the agent towards the at least one target state. The behavior of the artificial agent is self-determined such that the agent selects a next action to change the position in the state space on the landmark target of the medical image to maximize the total cumulative future reward. The maximized reward may, but not necessarily, minimize the total number of actions that must be taken by the agent to reach its goal of identifying the location of a target landmark within an image.

[0068] In act B909, the learned artificial agent is applied on a test image to automatically parse image content. The learned artificial agent can thus identify the target state and/or if the target state does not exist within the test image. The test image, unlike the training image, does not have any predetermined target states identified and may not contain a target state (e.g., landmark target) at all. Test images may be, but are not limited to, medical image scans of patients.

[0069] An episodic trajectory is explored in act B911 for a training image based on the completed evaluation of each portion of the training image via the state space. The episodic trajectory is indicative of the actions of the artificial agent as a sequence of visited states of the training image. Act B911 may be conducted by storing, in act B912, episodic trajectories at pre-defined intervals of sequential completed evaluations of training images by the artificial agent and updating, in act B913, parameters of the optimal action-value function approximator based on the stored episodic trajectories.

[0070] FIG. 2 illustrates a flow diagram in accordance with disclosed embodiments for generating an artificial agent for intelligent image parsing. The acts are performed in the order shown or other orders. Additional, different, or fewer acts may be provided. For example, the act B1005 may be performed in a different way than provided by act B1006. FIG. 10 illustrates acts that may be performed as part of defining the optimal action-value function approximator (act B907) of the method of FIG. 9 including a reference update delay feature of the defined optimal action-value function approximator of act B907 in FIG. 9. Accordingly, FIG. 10 may be performed as part of the method of FIG. 9.

[0071] In act B1001, the optimal action-value function approximator is evaluated for each current position of the state space. In act B1003, the optimal action-value function approximator is simultaneously obtained for all possible actions in each current state space. In act B1005, a reward policy of the optimal action-value function approximator is applied. Applying the reward policy of the optimal action-value function approximator of act B1005 may optionally include act B1006, in which the next action of the artificial agent is determined based on a balance of maximization the cumulative future reward value based on the reward system and completion of evaluation of each portion of each training image based on the state space.

[0072] FIG. 11 illustrates a flow diagram in accordance with another embodiment for generating an artificial agent for intelligent image parsing. The acts are performed in the order shown or other orders. Additional, different, or fewer acts may be provided. For example, the acts of FIG. 11 may be performed as part of the method of FIGS. 9 and/or FIG. 10. FIG. 11 illustrates acts that may be performed in conjunction with the method including an experience replay feature that may be included in defining the optimal action-value function approximator. In act B1101, experience memory database is generated including a pre-defined number of last evaluated states for current training image. In act B1103, the experience memory database is sampled. In act B1105, parameters of the optimal action-value function approximator are updated based on the experience memory. Experience memory may be partially or completely stored on memory 52.

[0073] The methods of FIGS. 9-11 provide method for intelligent landmark identification in medical images. The artificial agent is trained using a set of test images to optimize the behavior of the artificial agent and train the artificial agent to recognize a specific anatomical landmark target using marked examples of the anatomic landmark target on each training image. FIG. 12 illustrates a flow diagram in accordance with an embodiment of a method for training the artificial agent of the preceding figures for landmark identification in medical images. The acts are performed in the order shown or other orders. Additional, different, or fewer acts may be provided. For example, the training method of FIG. 12 may be conducted as part of the method of one or more of FIGS. 9-11.

[0074] Regarding FIG. 12, in act B1201, the state space of discrete portions of each training image of a set of training images are evaluated within the position of the state space. Training images include a landmark target pre-marked on each training image. Landmark targets are pre-marked in the training data set prior to training of the artificial agent. Once trained, the artificial agent may be used to evaluate medical images of patients in order to identify the same landmark target for which the artificial agent was trained. In act B1203, a position of the state space is changed with respect to the training image via application an action of a pre-defined set of actions. In act B1205, a reward value of each position change of the state space is determined. The reward value is based on a proximity of the current state space to a pre-defined landmark target of the training image. In act B1207, behavior of the artificial agent is optimized based on maximizing a cumulative future reward value based on the reward system, the set of actions, the state space, and a set of training images. The behavior of the artificial agent is the intelligent selection of next actions that achieve a position of the state space on a landmark target in a medical image of a patient in such a way that the cumulative future reward is maximized. That is, the artificial agent learns to determine the most favorable sequence of position changes required to accurately detect a landmark target.

[0075] In one embodiment, medical images are evaluated by an artificial image. Medical images of a patient are received by processor 50. Images may be captured via imaging system 48, stored in memory 52 or obtained over a wireless or wired network. The processor 50 applies optimized behavior of an artificial agent. The applied behavior includes selecting actions from a pre-defined set of actions changing the position of the state space relative to the medical image. Applied behavior may include evaluating discrete portions of the medical image defined by a position of the state space of the artificial agent relative to the medical image, and determining a location of the target landmark when present in the medical image from the evaluation. The identified landmark, medical image and/or other information obtained during analysis by processor 50 may be displayed on display 54. User interaction with the resulting located target landmark or image may be annotated via user input to display 54 or via a peripheral device connected to processor 50. Determination of a location of the target landmark may include identifying oscillations of the artificial agent between adjacent state space positions. The cumulative reward value of the artificial agent of the adjacent state space positions of the identified oscillations may further be determined. The landmark target may then be identified on the medical image of the patient when the cumulative reward value indicates a proximity of the adjacent state space within a pre-defined reward threshold distance value of the landmark target on the medical image. An indication that the boundary of a target space (e.g., target anatomical object) is partially or fully within the medical image.

[0076] The target landmark is not present in the medical image when the cumulative reward value is outside a pre-defined failure threshold distance value. An indication may be generated indicating that the target landmark is not present in the medical image.

[0077] Detailed description of various techniques employed by the disclosed embodiments depicted above and in FIGS. 9-12 are discussed below.

[0078] State Space

[0079] A state space is modeled as a candidate position for the landmark target and a fixed region around the candidate position. For example, a state space for a two-dimensional medical image application may be a square window (i.e., square patch) with a defined width and length in pixels. The candidate position for the state space is the coordinate point in the center of the square. Evaluation of a state space is an evaluation for the candidate position, representing a focal point of the agent.

[0080] A state space is defined by parameters of height and width of 60×60 pixels. A state space defined as additional or different parameters and may be generalized to any kind of parametric space. Other parameters defining a state space may include location, or rotation. Image data may have a margin, or pixel border (e.g., 30 pixel wide black margin for use with 60×60 pixel patch) so that the center of the moving window can effectively reach the edge of the image.

[0081] The artificial agent evaluates image data, selectively observes and evaluates the image data defined by the agent's current state space with respect to the image data. The agent's subsequent behavior for the candidate position is responsive to what is observed within the state space. A state space needs to be discriminative in order to limit the amount of data, minimizing computational load of the evaluation (rather than analyzing the entire image data set). The state space is self-describing based on its parameters to provide a context for the evaluation of image data at the current position of the state space. The state space is composed of parameters that are used to establish a focal point (e.g., one particular coordinate, pixel, or voxel), while also permitting limited perception of the surrounding context (state space dimension in a size and shape such as a pixel, or voxel). Similar to animal and human visual perception systems, dense local information is captured around a focal point and limited global context associated from the surrounding neighborhood is acquired without acquiring all available global information.

[0082] A locality assumption is made and a state observed at time t as s_t=(l_t, x_t, y_t, l_t), i.e., a local patch of size l_t×l_t centered at position (x_t, y_t) in the observed image I_t. States which are close to the target landmark location will directly capture the position of the landmark in their context. For distant states, the relation to the landmark location is intrinsic, captured indirectly by information from the context of the current patch.

[0083] Set of Actions

[0084] In each state space, the agent interacts with the enclosed environment of an image by selecting and performing actions from a pre-defined set of actions. The set of actions is chosen in such a way that the agent is given the possibility to explore the entire environment. Located in state s_t at time t, (for a visual goal of identifying the location of a target landmark), the agent may a set of actions may be defined as the discrete actions of changing the position of the focal point of the state space by one pixel in a direction specified as: upwards, downwards, left, or right with respect to the training or test image. An action set may be defined to include an action that permits the agent to select non-action, staying at the same position. Each action is simplified to a single pixel move: x_t+1←x_t±1 and y_t+1←y_t±1. Once the target has been reached, no further action is performed, and the search is finished. Additional or alternative actions may include rotation around an axis, movement of multiple pixels in each action, and/or scaling. Actions may include multiple discrete steps and/or may occur simultaneously. Choices of action set may be selected that are not optimal. However, limitation of the action set is not limiting to the embodied method, as the present action set permits iteration and exploration of the entire content of the image.

[0085] Rewards

[0086] The reward system is based on the change in relative position at state s_t: (x_t, y_t) with respect to the target position of the landmark s_target:(x_target,y_target). Intuitively, for a move in the correct direction, a positive reward proportional to the target-distance reduction is given, whereas a move in the wrong direction is punished by a negative reward of equal magnitude. The reward at time t is given by Equation 7:
r_t=dist(s_t,s_target)−dist(s_t+1,s_target)  Eq. 7

[0087] Exceptions to this rule may be additionally provided. For example, in one embodiment, the only exception to this rule is an attempt to leave the image field by crossing the image border. This action is always given the highest punishment of −1. The reward is correlated to the goodness of a performed action, providing a complex trial-error system, simulating the human experience more closely. Good actions, contribute significantly towards reaching the goal, are given a high reward, whereas actions that only marginally improve the state of the agent, receive little reward. This reward system is more complex compared to a simple ±1 reward used in some conventional methods.

[0088] Rewards increase in or decrease based on distance to target position. Changes in accumulated rewards provide reinforcement learning for the agent to quantify its moves.

[0089] Deep Reinforcement Learning

[0090] The disclosed embodiments include both DL and RL, to provide a system using deep reinforcement learning. Given the state space, set of actions, and reward system, the goal of the agent is to learn how to identify the location of an anatomical landmark in a set of image data and to also automate the optimization of a method for efficiently identifying the anatomical landmark. That is, the agent, during training, both learns to identify the location of an anatomical landmark and determines a method to select the actions needed to traverse the image data in order to successfully identify the anatomical landmark (e.g., the agent determines a method for using) select actions and simultaneously itself for feature extraction by repeatedly interacting with the enclosed environment in order to maximize cumulative future reward (see, Eq. 4). This optimal behavior is defined by the optimal policy π* selected from the space of all possible policies π←p(action|state). As in Equation 5, the agent develops its own optimal policy for a training data set based on the optimal action-value function Q*.

[0091] The disclosed embodiments are model-free, temporal difference approaches that use a deep convolutional neural network (CNN) to approximate the optimal action-value function Q*. The parameters of a deep CNN may be defined as θ=[({right arrow over (ω)}, {right arrow over (b)}], where {right arrow over (ω)} represents the weights of the network, and {right arrow over (b)} defines the biases of the neurons. This architecture is used as a generic, non-linear function that approximates Q(s, a; θ)≈(s, a), called deep Q network (DQN). Reference update-delay and experience replay are used to account for possible divergence issues during training.

[0092] Visualization of the optimal action-value function Q* are depicted in FIGS. 8A-8D. Visualizations 810, 820, 830 and 840 are Q*-fields indicating the highest expected reward considering all actions allowed in that state space (i.e., the highest expected reward for the center point of each possible position of the state space) for images 815, 825, 835, and 845. FIGS. 8A and 8B illustrate convergence at the LV-center and the posterior RV-insertion point corresponding to the landmarks of FIG. 3A. Convergence is illustrated as the global minimum point reaches near zero-values at the location of the target landmark, depicted as an X on the projected MR image. The Q*-fields of FIGS. 3C and 3D are also representative of target landmark goals for the LV-center and posterior RV-insertion point, respectively. However, images 835 and 845 do not contain the target landmark, so the Q*-fields do not approach zero at any point in the images.

[0093] Similar to the temporal difference Q-Learning algorithm, a deep Q network can be trained in a reinforcement learning setup using an iterative approach to minimize the mean squared error based on the Bellman optimality criterion as in Eq. 6. At any iteration i, the optimal expected target values can be approximated using a set of reference parameters θ_i^ref:=θ_j from a previous iteration j<i provided in Equation 8:
y=r+γ max_a′Q(s′,a′;θ_i^ref)  Eq. 8

[0094] A sequence of well-defined optimization problems drives the evolution of the network parameters. The function at each step i is defined as Equation 9:
θ=min_{θis,a,r,s′}[(y−Q(s,a;θ_i))²]+_s,a,r[_s′[y]]  Eq. 9

[0095] This supervised setup for deep learning combines a mini-batch gradient-based approach with back propagation. Stochastic gradient descent steps are periodically applied, approximating the gradient by randomly sampling the gradient function, given as Equation 10:
∇_θiErr(θ_i)=_s,a,r,s′[(y=Q(s,a;θ_i))∇_θiQ(s,a;θ_i)]  Eq. 10
where Err(θ_i) represents the error function introduced in Equation 9.

[0096] At the beginning of training, the agent freely navigates through the space at random. That is, no operator or user input is required. Instead, gradually during training, the agent learns a policy, which tells the agent what is correct. Initial test images used for training require pre-marked annotations identifying x,y ground truth (e.g., the target landmark).

[0097] Reference Update-Delay

[0098] Use of a different network to compute the reference values for training provides robustness to the algorithm. Changes to the current parameters θ_i and implicitly to the current approximator Q(•; θ_i) cannot directly impact the reference output y, introducing update-delay and thereby reducing the probability to diverge obsolete and suboptimal regions of the optimization space.

[0099] FIG. 2, is a more in-depth visualization of the main system diagram introduced in FIG. 1. In a given state, specified by the current view patch, the neural network is evaluated on that particular patch to simultaneously obtain Q* value estimates for all possible actions: Q(s, a₁), Q*(s, a₂), . . . . Given the estimates, the agent applies ε-greedy policy, choosing a random action with probability ε and following the current policy estimation (choosing the action with the next future, discounted reward) with probability 1−ε. During learning, a value decay is applied on the parameter E reaching a trade-off between an effective space exploration in a greedy, consistent policy exploitation strategy.

[0100] Experience Replay

[0101] Frequent updates of the parameters to the optimal action-value function approximator facilitates more efficient artificial agent training. Experience replay may be used in some embodiments. In this experience replay, the agent stores a limited amount of previously visited states (e.g., the last dates), the so-called experience memory, and then samples that memory to update the parameters of the underlying neural network. Learning takes place in a sequence of episodes that quantify the local performance of the agent on given training images. Before the start of one episode, the agent is given a random image from the complete training set at any random start state, e. g., start position in that image. During the course of the episode, the agent performs actions applying the ε-greedy behavior policy navigating through this local environment (the given training image). The episode finishes when the target state is reached, in other words the landmark location is found, or a predefined maximum number of actions are executed. A target state may be an anatomical landmark, an anatomical object, a region, point, area, or volume. The target state may be a comprehensive template of measurements from image parsing and the set of actions may include changes of the parameters available to product the optimal set of measurements. This defines a so-called trajectory t_i (also called episodic trajectory) in image space that includes the applied search strategy as a sequence of visited states. These trajectories are stored in replay memory, representing the entire experience the agent has accumulated on different images. In some embodiments, the last P trajectories are stored as E=[t₁, t₂, . . . , t_p]. At fixed intervals during training (e.g., every 4-6 state transitions), a perimeter update is performed using a random mini-batch of states extracted from E. This approach achieves the goal of ensuring training convergence. Updating the deep neural network on locally correlated states (similar to Q-learning) does not generalize. Instead, performance of the network in other parts of the state space are strongly affected. Using a uniformly sampled set of previous experiences, averages the distribution of the network input, and reducing oscillations ensure a faster and robust learning experience.

[0102] Image Modalities

[0103] While the disclosed embodiments are described in the context of anatomical landmark detection, other applications of these embodiments may be used in the context of image analysis and general image understanding. For example, (simultaneous) object detection and segmentation may be applied to quantifying image analysis limitations in terms of accuracy, result confidence, policy performance, and optimization of general computational requirements. The disclosed embodiments are further applicable to a variety of action sets.

[0104] The disclosed embodiments of medical image parsing (e.g., landmark detection), training of intelligent, generic agents overcome the limitations of predefined, standard machine learning approaches. Using Q-learning based framework deep learning techniques directly approximate the optimal behavior of the agent in a trial-and-error environment, describing the underlying problem. The artificial agent of the disclosed embodiments is adaptable to different landmarks from different image modalities, such that the artificial agent is capable of automatically discovering and developing strategies for landmark detection at high accuracy while simultaneously evaluating the medical image using the strategy. These agents may extend the framework on a wide range of image analysis applications, creating agents that can solve multiple problems in an intelligent, principled way.

[0105] The disclosed embodiments are additionally robust for use with other multi-dimensionalities. For example, a goal is achieved by providing a system capable of generating an artificial agent capable of scaling execution of learning and executing image analysis of a two-dimensional dataset. A goal is further achieved providing a flexible enough artificial agent capable of learning and executing image analysis of a two-dimensional dataset as well as in three-dimensional dataset without fundamentally changing the structure of the system. Only changes in the identification data are necessary, such as establishing a landmark target location based on a three-dimensional location (e.g. a three-dimensional point or a voxel), instead of a two-dimensional target location (e.g., a two-dimensional location or a pixel). Additional actions or sets of actions, may be applicable to some applications but not others, such as three-dimensional rotation of the state space with respect to its position within a three-dimensional image. While different agents are trained for each individual target landmarks, the process generating and training the artificial agent is naturally and self-adaptive requiring no fundamental changes to establish a structure of the artificial agent's learning process and training based on a specific task or image modality.

[0106] Experience Based Adaptive Agents

[0107] The disclosed system using artificial agents may be further adaptive in some embodiments to further optimize repeated user input, workflows, or other environment or local requirements. Techniques described above with respect to self-determining optimization methods may be further employed to customize annotation behavior, repeat image quality settings, self-optimize workflows based on local environments, and interact with the user or local population of users associated with use of artificial agents or post-processing diagnosis or analysis associated with the detected anatomical landmark target. An agent may generate an annotation indicative of the determine location of the target landmark in the medical image and provide the medical image and generated annotation for display.

[0108] Adaptation based on user experience may be localized with respect to a single workstation or processor or may be aggregated from multiple similar systems. User based preferences may require identification protocols such as user id/password entry, facial recognition, biometric sensor identification or user identification protocols. Some adaptivity, such as application or task centric adaptivity, may not require individual user identification. Adaptation may be further localized based on country, hospital, type of medical profession, medical specialty or other group exhibiting similar usage characteristics.

[0109] Experience based adaptivity may include assimilation of model behavior and optimization of individual, repeated interactions with the system. These gradual personalization models may optimize personalization strategy through repeated interaction, or may prompt the user to create personalized models for individual users or patients.

[0110] User interactions may include pre-defining one or more actions in a set of actions for target state location identification. Users may select or identify an action via providing input to an imaging system 48. Users may also annotate images prior to training, following training, prior to testing, or following testing of an image. The artificial agent may learn, via methods disclosed above, example annotation actions received via user input to imaging system 48 or selection of image optimization parameters such as contrast, size, brightness or other parameter of a test image or training image.

[0111] User inputs to an imaging system 48 may be observed by the artificial agent and an optimal action-value function approximator may specify the behavior of the artificial agent based on the observed input. The user entered inputs may be replicated by the agent. The artificial agent, may suggest a next action of the processor based on the replicated user inputs.

Device and System Architecture

[0112] FIG. 13 depicts a system for generating and training an artificial agent for intelligent image parsing and evaluating medical images of a patient via the artificial agent, such as locating ventricle landmarks on a medical image scan of a patient's heart. The system includes an imaging system 48, a memory 52, an image processor 50, and a display 54. Additional, different, or fewer components may be provided. For example, a network or network connection is provided, such as for networking with a medical imaging network or data archival system. In another example, a user interface is provided.

[0113] The image processor 50, memory 52, and display 54 are part of the medical imaging system 48. Alternatively, the image processor 50, memory 52, and/or display 54 are part of an archival and/or image processing system, such as associated with a medical records database workstation or server. In other embodiments, the image processor 50, memory 52, and/or display 54 are a computer, such as desktop or laptop, a workstation, a server, a network, or combinations thereof

[0114] The imaging system 48 is a medical diagnostic imaging system. Ultrasound, computed tomography (CT), x-ray, fluoroscopy, positron emission tomography, single photon emission computed tomography, and/or magnetic resonance (MR) systems may be used. The imaging system 48 may include a transmitter and includes a detector for scanning or receiving data representative of the interior of the patient.

[0115] In one embodiment, the imaging system 48 is a CT system. An x-ray source is connected with a gantry. A detector is also connected with the gantry opposite the x-ray source. The patient is positioned between the source and detector. The source and detector are on opposite sides of the patient and rotate about the patient. The detected x-ray energy passing through the patient is reconstructed or transformed into data representing different spatial locations within the patient.

[0116] In another embodiment, the imaging system 48 is an MR system. The MR system includes a main field magnet, such as a cryomagnet, and gradient coils. A whole body coil is provided for transmitting and/or receiving. Local coils may be used, such as for receiving electromagnetic energy emitted by atoms in response to pulses. Other processing components may be provided, such as for planning and generating transmit pulses for the coils based on the sequence and for receiving and processing the received k-space data. The received k-space data is converted into object or image space data with Fourier processing.

[0117] The memory 52 may be a graphics processing memory, a video random access memory, a random access memory, system memory, cache memory, hard drive, optical media, magnetic media, flash drive, buffer, database, combinations thereof, or other now known or later developed memory device for storing image data, artificial agents, and/or data and programs for generating and/or training an artificial agent. The memory 52 is part of the imaging system 48, part of a computer associated with the processor 50, part of a database, part of another system, a picture archival memory, or a standalone device.

[0118] The memory 52 or other memory is alternatively or additionally a non-transitory computer readable storage medium storing data representing instructions executable by the programmed processor 50 for generating and training an artificial agent for intelligent image parsing and evaluating medical images of a patient via the artificial agent. The instructions for implementing the processes, methods and/or techniques discussed herein are provided on non-transitory computer-readable storage media or memories, such as a cache, buffer, RAM, removable media, hard drive or other computer readable storage media. Non-transitory computer readable storage media include various types of volatile and nonvolatile storage media. The functions, acts or tasks illustrated in the figures or described herein are executed in response to one or more sets of instructions stored in or on computer readable storage media. The functions, acts or tasks are independent of the particular type of instructions set, storage media, processor or processing strategy and may be performed by software, hardware, integrated circuits, firmware, micro code and the like, operating alone, or in combination. Likewise, processing strategies may include multiprocessing, multitasking, parallel processing, and the like.

[0119] In one embodiment, the instructions are stored on a removable media device for reading by local or remote systems. In other embodiments, the instructions are stored in a remote location for transfer through a computer network or over telephone lines. In yet other embodiments, the instructions are stored within a given computer, CPU, GPU, or system.

[0120] The image processor 50 is a general processor, central processing unit, control processor, graphics processor, digital signal processor, three-dimensional rendering processor, image processor, application specific integrated circuit, field programmable gate array, digital circuit, analog circuit, combinations thereof, or other now known or later developed device for generating and training an artificial agent for intelligent image parsing and evaluating medical images of a patient via the artificial agent. The image processor 50 is a single device or multiple devices operating in serial, parallel, or separately. The image processor 50 may be a main processor of a computer, such as a laptop or desktop computer, or may be a processor for handling some tasks in a larger system, such as in an imaging system. The image processor 50 is configured by instructions, design, hardware, and/or software to perform the acts discussed herein.

[0121] The image processor 50 is configured to implement the acts of the preceding figures. For example, the image processor 50 is configured to generate an artificial agent for intelligent image parsing as in accordance with the method of FIGS. 9-11. The image processor 50 may be alternatively or additionally configured to implement training of the artificial agent is illustrated in FIG. 12.

[0122] As of the solution, the image processor 50 interacts with the medical imaging system 48 or other source of scan data, stores data in different parts of the memory 52, and generates output to assist in medical diagnosis and/or therapy. Manual segmentation is highly inefficient, not cost effective, and uses different processes than the technical solution.

[0123] The display 54 is a monitor, LCD, projector, plasma display, CRT, printer, or other now known or later developed devise for outputting visual information. The display 54 receives images, graphics, text, quantities, or other information from the processor 50, memory 52, or imaging system 48. One or more medical images are displayed. The images are of a region of the patient, such as images of the heart. The image includes an indication, such as a graphic or colorization, of the boundary or other segmentation. Alternatively, or additionally, the image includes a quantity based on the boundary. The quantity may be displayed as the image without the medical image representation of the patient.

[0124] While the invention has been described above by reference to various embodiments, it should be understood that many changes and modifications can be made without departing from the scope of the invention. It is therefore intended that the foregoing detailed description be regarded as illustrative rather than limiting, and that it be understood that it is the following claims, including all equivalents, that are intended to define the spirit and scope of this invention.